Apparatus for treating a respiratory disorder with a power source connection

ABSTRACT

A respiratory device, such as a ventilator, for use in treating respiratory disorders and for preventing respiratory disorders. The respiratory device is configured to be powered from a range of different power sources including an internal battery, an external battery, AC power source or a DC power source. The device may be electrically connectable to a plurality of external batteries in a series and the power from each external battery is used sequentially along the series. A controller of the respiratory device is configured to detect the connection of the different power sources and control use of the different power sources using a power priority scheme. The controller may determine an estimate of the total available battery capacity from all the electrically connected batteries and display the total battery capacity on a user interface display of the device.

1 CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation application of U.S. application Ser.No. 14/528,573, filed Oct. 30, 2014, now allowed; which claims priorityto European Patent Application No. 13 30 6491.5, filed 31 Oct. 2013, theentire contents of which are hereby incorporated herein by reference.

2 COPYRIGHT NOTICE

A portion of the disclosure of this patent document contains materialwhich is subject to copyright protection. The copyright owner has noobjection to the facsimile reproduction by anyone of the patent documentor the patent disclosure, as it appears in the Patent and TrademarkOffice patent file or records, but otherwise reserves all copyrightrights whatsoever.

3 BACKGROUND OF THE INVENTION 3.1 Field of the Invention

The present technology relates to one or more of the diagnosis,treatment and amelioration of respiratory disorders, and to proceduresto prevent respiratory disorders. In particular, the present technologyrelates to medical devices, and their use for treating respiratorydisorders and for preventing respiratory disorders.

3.2 Description of the Related Art

The respiratory system of the body facilitates gas exchange. The noseand mouth form the entrance to the airways of a patient.

The airways include a series of branching tubes, which become narrower,shorter and more numerous as they penetrate deeper into the lung. Theprime function of the lung is gas exchange, allowing oxygen to move fromthe air into the venous blood and carbon dioxide to move out. Thetrachea divides into right and left main bronchi, which further divideeventually into terminal bronchioles. The bronchi make up the conductingairways, and do not take part in gas exchange. Further divisions of theairways lead to the respiratory bronchioles, and eventually to thealveoli. The alveolated region of the lung is where the gas exchangetakes place, and is referred to as the respiratory zone. See West,Respiratory Physiology—the essentials.

A range of respiratory disorders exist.

Obstructive Sleep Apnea (OSA), a form of Sleep Disordered Breathing(SDB), is characterized by occlusion or obstruction of the upper airpassage during sleep. It results from a combination of an abnormallysmall upper airway and the normal loss of muscle tone in the region ofthe tongue, soft palate and posterior oropharyngeal wall during sleep.The condition causes the affected patient to stop breathing for periodstypically of 30 to 120 seconds duration, sometimes 200 to 300 times pernight. It often causes excessive daytime somnolence, and it may causecardiovascular disease and brain damage. The syndrome is a commondisorder, particularly in middle aged overweight males, although aperson affected may have no awareness of the problem. See U.S. Pat. No.4,944,310 (Sullivan).

Cheyne-Stokes Respiration (CSR) is a disorder of a patient's respiratorycontroller in which there are rhythmic alternating periods of waxing andwaning ventilation, causing repetitive de-oxygenation and re-oxygenationof the arterial blood. It is possible that CSR is harmful because of therepetitive hypoxia. In some patients CSR is associated with repetitivearousal from sleep, which causes severe sleep disruption, increasedsympathetic activity, and increased afterload. See U.S. Pat. No.6,532,959 (Berthon-Jones).

Obesity Hyperventilation Syndrome (OHS) is defined as the combination ofsevere obesity and awake chronic hypercapnia, in the absence of otherknown causes for hypoventilation. Symptoms include dyspnea, morningheadache and excessive daytime sleepiness.

Chronic Obstructive Pulmonary Disease (COPD) encompasses any of a groupof lower airway diseases that have certain characteristics in common.These include increased resistance to air movement, extended expiratoryphase of respiration, and loss of the normal elasticity of the lung.Examples of COPD are emphysema and chronic bronchitis. COPD is caused bychronic tobacco smoking (primary risk factor), occupational exposures,air pollution and genetic factors. Symptoms include: dyspnea onexertion, chronic cough and sputum production.

Neuromuscular Disease (NMD) is a broad term that encompasses manydiseases and ailments that impair the functioning of the muscles eitherdirectly via intrinsic muscle pathology, or indirectly via nervepathology. Some NMD patients are characterised by progressive muscularimpairment leading to loss of ambulation, being wheelchair-bound,swallowing difficulties, respiratory muscle weakness and, eventually,death from respiratory failure. Neuromuscular disorders can be dividedinto rapidly progressive and slowly progressive: (i) Rapidly progressivedisorders: Characterised by muscle impairment that worsens over monthsand results in death within a few years (e.g. Amyotrophic lateralsclerosis (ALS) and Duchenne muscular dystrophy (DMD) in teenagers);(ii) Variable or slowly progressive disorders: Characterised by muscleimpairment that worsens over years and only mildly reduces lifeexpectancy (e.g. Limb girdle, Facioscapulohumeral and Myotonic musculardystrophy). Symptoms of respiratory failure in NMD include: increasinggeneralised weakness, dysphagia, dyspnea on exertion and at rest,fatigue, sleepiness, morning headache, and difficulties withconcentration and mood changes.

Chest wall disorders are a group of thoracic deformities that result ininefficient coupling between the respiratory muscles and the thoraciccage. The disorders are usually characterised by a restrictive defectand share the potential of long term hypercapnic respiratory failure.Scoliosis and/or kyphoscoliosis may cause severe respiratory failure.Symptoms of respiratory failure include: dyspnea on exertion, peripheraloedema, orthopnea, repeated chest infections, morning headaches,fatigue, poor sleep quality and loss of appetite.

Otherwise healthy individuals may take advantage of systems and devicesto prevent respiratory disorders from arising.

3.2.1 Systems

One known product used for treating sleep disordered breathing is the S9Sleep Therapy System, manufactured by ResMed. Ventilators such as theResMed Stellar™ Series of Adult and Paediatric Ventilators may providesupport for invasive and non-invasive non-dependent ventilation for arange of patients for treating a number of conditions such as but notlimited to NMD, OHS and COPD.

The ResMed Elisée™ 150 ventilator and ResMed VS III™ ventilator mayprovide support for invasive and non-invasive dependent ventilationsuitable for adult or paediatric patients for treating a number ofconditions. These ventilators provide volumetric and barometricventilation modes with a single or double limb circuit.

3.2.2 Therapy

Nasal Continuous Positive Airway Pressure (CPAP) therapy has been usedto treat Obstructive Sleep Apnea (OSA). The hypothesis is thatcontinuous positive airway pressure acts as a pneumatic splint and mayprevent upper airway occlusion by pushing the soft palate and tongueforward and away from the posterior oropharyngeal wall.

Non-invasive ventilation (NIV) provides ventilator support to a patientthrough the upper airways to assist the patient in taking a full breathand/or maintain adequate oxygen levels in the body. The ventilatorsupport is provided by a mask or nasal interface. NIV has been used totreat OHS, COPD, MD and Chest Wall disorders. Invasive ventilation (IV)provides ventilatory support to patient's that are no longer able toeffectively breathe themselves and is provided using a tracheostomy tubeor an endotracheal tube.

Ventilators also control the timing and pressure of breaths pumped intothe patient and monitors the breaths taken by the patient. The methodsof control and monitoring patients typically include volume-cycled andpressure-cycled methods. The volume-cycled methods may include amongothers, Pressure-Regulated Volume Control (PRVC), Volume Ventilation(VV), and Volume Controlled Continuous Mandatory Ventilation (VC-CMV)techniques. The pressure-cycled methods may involve, among others,Assist Control (AC), Synchronized Intermittent Mandatory Ventilation(SIMV), Controlled Mechanical Ventilation (CMV), Pressure SupportVentilation (PSV), Continuous Positive Airway Pressure (CPAP), orPositive End Expiratory Pressure (PEEP) techniques.

3.2.3 Patient Interface

The application of a supply of air at positive pressure to the entranceof the airways of a patient is facilitated by the use of a patientinterface, such as a nasal mask, full-face mask or nasal pillows. Arange of patient interface devices are known, however a number of themsuffer from being one or more of obtrusive, aesthetically undesirable,poorly fitting, difficult to use and uncomfortable especially when wornfor long periods of time or when a patient is unfamiliar with a system.Masks designed solely for aviators, as part of personal protectionequipment or for the administration of anaesthetics may be tolerable fortheir original application, but nevertheless be undesirablyuncomfortable to be worn for extended periods, for example, whilesleeping or throughout the day.

A tracheostomy tube or endotracheal tube are other forms of patientinterfaces that may be used for invasive ventilation.

3.2.4 Devices

The air at positive pressure may be supplied to the airway of a patientby a Positive airway pressure (PAP) device such as a motor-drivenblower. The outlet of the blower is connected via a flexible deliveryconduit to a patient interface as described above.

Ventilators typically include a flow generator, an inlet filter, apatient interface, an air delivery conduit connecting the flow generatorto the patient interface, various sensors and a microprocessor-basedcontroller. The patient interface may include a mask, nasal prongs or atracheostomy or endotracheal tube as described above. The flow generatormay include a servo-controlled motor, volute and an impeller that formsa blower. In some cases a brake for the motor may be implemented to morerapidly reduce the speed of the blower so as to overcome the inertia ofthe motor and impeller. The braking can permit the blower to morerapidly achieve a lower pressure condition in time for synchronizationwith expiration despite the inertia. In some cases the flow generatormay also include a valve capable of discharging generated air toatmosphere as a means for altering the pressure delivered to the patientas an alternative to motor speed control. The sensors measure, amongstother things, motor speed, mass flow rate and outlet pressure, such aswith a pressure transducer or the like. The apparatus may optionallyinclude a humidifier and/or heater elements in the path of the airdelivery circuit. The controller may include data storage capacity withor without integrated data retrieval and display functions.

3.2.5 Humidifier

Respiratory apparatuses commonly have the ability to alter the humidityof the breathable gas in order to reduce drying of the patient's airwayand consequent patient discomfort and associated complications. Ahumidifier may be located between the flow generator or PAP device orventilator and the patient interface or before the flow generator or PAPdevice or Ventilator. The use of a humidifier produces humidified gasthat minimizes drying of the nasal mucosa and increases patient airwaycomfort. In addition in cooler climates, warm air applied generally tothe face area in and about the patient interface is more comfortablethan cold air.

Humidity refers to the quantity of water vapour present in the air. Itis commonly measured in two ways:

-   -   (1) Absolute Humidity (AH) is the actual content of water        recorded in terms of weight per volume—usually in grams per        cubic meter (g/m3) or milligrams per liter (mg/L).    -   (2) Relative Humidity (RH) is a percentage expression of the        actual water vapour content of a gas compared to its capacity to        carry water at any given temperature.

The capacity of air to hold water vapour increases as the temperature ofthe air increases. This means that for air with a stable AH, the RH willdecline as the temperature of the air is increased. Conversely, for airsaturated with water (100% RH), if the temperature is reduced then theexcess water will condense out. Air breathed by humans is generallynaturally heated and humidified by the airway to reach a temperature of37° C. and 100% humidity. At this temperature the AH humidity is 44mg/L.

Respiratory humidifiers are available in many forms and may be astandalone device that is coupled to a respiratory device via a airdelivery tube, is integrated with the respiratory device or configuredto be directly coupled to the relevant respiratory apparatus. Whilepassive humidifiers can provide some relief, generally a heatedhumidifier is required to provide sufficient humidity and temperature tothe air so that the patient will be comfortable. Humidifiers typicallycomprise a water reservoir or tub having a capacity of several hundredmilliliters (ml), a heating element for heating the water in thereservoir, a control to enable the level of humidification to be varied,a gas inlet to receive gas from the flow generator or device, and a gasoutlet adapted to be connected to an air delivery conduit that deliversthe humidified gas to the patient interface.

Heated passover humidification is one common form of humidification usedwith a PAP device. In such systems the heating element may beincorporated in a heater plate which sits under, and is in thermalcontact with, the water tub. Thus, heat is transferred from the heaterplate to the water reservoir primarily by conduction. The air flow fromthe PAP device or flow generator or ventilator passes over the heatedwater in the water tub resulting in water vapour being taken up by theair flow. The ResMed H4i™ and H5i™ Humidifiers are examples of suchheated passover humidification systems that are used in combination withResMed S8 and S9 CPAP systems respectively.

Other humidification systems may also be used such as a bubble ordiffuser humidifier, a jet humidifier or a wicking humidifier.

An alternative form of humidification is provided by the ResMedHumiCare™ D900 humidifier that uses a CounterStream™ technology thatdirects the air flow over a large surface area in a first directionwhilst supplying heated water to the large surface area in a secondopposite direction. The ResMed HumiCare™ D900 humidifier may be usedwith a range of invasive and non-invasive ventilators.

3.2.6 Air Circuits

Air circuits may include a single limb circuit or air delivery conduitas shown in FIG. 1. A single limb circuit may be used with anintentional leak vent. The vent may be provided as an independent part,such as an anti-asphyxia valve, fitted to an air delivery tube or thevent may be incorporated in as part of the patient interface. The airdelivery tube is connected to the outlet of the device, e.g. ventilatoror humidifier. In this single limb circuit arrangement the inspiratoryair or gas is from the device through the air delivery conduit to thepatient interface for delivery to the patient and the patient's exhaledgas is exhausted through the vent. The ventilator provides a positivepressure at the vent to ensure the patient exhalant is exhausted.

In an alternative arrangement a single limb circuit may be used with aproximal pneumatic valve. The proximal pneumatic valve is provided nearthe patient interface end of the air delivery conduit. The opposite endof the air delivery tube is connected to the outlet of the device, e.g.ventilator or humidifier. A small tube is also connected between thedevice and the proximal pneumatic valve to provide a pressure controlline. The device applies a control pressure to the proximal pneumaticvalve to control opening and closing of an exhaust port of the proximalpneumatic valve. During inhalation, the valve is fully closed, directingall air flow to the patient interface. During exhalation, the valve isproportionally controlled to permit the patient to exhale out of theexhaust port but at a specified back-pressure (known as the Positive EndExpiratory Pressure (PEEP)). The ventilator also continues to output abias-flow to ensure accurate control of PEEP, and to offset anyunintentional leak at the patient interface. Air pressure at the patientmay be monitored, using a pressure sense line that is connected to aproximal pressure sensor within the ventilator.

In a further arrangement a double limb circuit may be used. A doublelimb circuit comprises two tubes: an inspiratory tube that delivers airfrom the ventilator to the patient during inspiration; and an expiratorytube that delivers expired air from the patient to an expiratory port ofthe ventilator and then out an exhaust port. Geometrically the two tubesmay be arranged side-by-side or co-axially. Air flow between theexpiratory port and the exhaust port may be regulated by a pneumaticvalve located internally within the ventilator.

During inspiration, the valve is fully closed, directing all air flow tothe patient. During expiration, the valve is proportionally controlledto permit the patient to exhale out of the exhaust port but at aspecified PEEP pressure. The ventilator also continues to output abias-flow to ensure accurate control of PEEP, and to offset anyunintentional leak at the patient interface. Air pressure at the patientmay be monitored during inspiration via a proximal pressure sensorwithin the ventilator connected to the expiratory tube; and duringexpiration via an output pressure sensor connected to the inspiratorytube.

Heated single limb or double limb air delivery circuits may also be usedto prevent rainout from occurring within the air delivery circuits.

4 BRIEF SUMMARY OF THE TECHNOLOGY

The present technology is directed towards providing medical devicesused in the diagnosis, amelioration, treatment, or prevention ofrespiratory disorders having one or more of improved comfort, cost,efficacy, ease of use and manufacturability.

A first aspect of the present technology relates to apparatus used inthe diagnosis, amelioration, treatment or prevention of a respiratorydisorder.

Another aspect of the present technology relates to methods used in thediagnosis, amelioration, treatment or prevention of a respiratorydisorder.

One form of the present technology comprises an apparatus for treating arespiratory disorder electrically connected to a plurality of externalbatteries connected in series.

Another aspect of one form of the present technology is a ventilatorcapable of being electrically connected to a plurality externalbatteries electrically connected in series.

Another aspect of one form of the present technology is a method ofdetermining an estimate of available battery capacity from two or morebattery power sources electrically connected to a respiratory device.Battery capacity may include for example battery remaining run time orbattery remaining charge.

Another aspect of one form of the present technology includes anapparatus for treating a respiratory disorder comprising a housing, auser interface display, a pressure source to provide a supply ofpressurized gas, a controller configured to control the pressure source,a power source connection configured to receive an electrical connectionof a power source to provide power for the apparatus, and a plurality ofexternal batteries electrically connected in a series to the powersource connection.

The controller of the apparatus may be configured to detect theconnection of the plurality of external batteries and control the supplyof power to the apparatus. Furthermore, in use the external battery ofthe plurality of external batteries being used to provide the supply ofpower for the apparatus may be the power supplying external battery andeach of the plurality of external batteries may be used as the powersource sequentially with the external battery closest to the powersource connection being the first external battery to be used as thepower source. Each external battery of the plurality of externalbatteries may be connected to an adjacent external battery using anelectrical cable. The external battery closest to the ventilator may bethe last external battery to be used. The recharging of the series ofexternal batteries may be performed in the reverse order, such that theexternal battery closest to the ventilator is recharged first.

In an alternative arrangement the external batteries may be used inseries as a power source with the external battery closest to theventilator being the first external battery to be used. The rechargingof the external batteries may also be performed in series with theexternal battery closest to the ventilator being recharged last.

In some aspect the apparatus may also comprise an internal batteryconfigured to be received within the housing and in use the internalbattery is used as the power source after all the power from theexternal batteries is depleted.

In some aspect the apparatus may also comprise an alternating current(AC) power supply connectable in the series to the plurality of externalbatteries, and in use when the AC power supply is connected the AC powersupply is used as the power source.

In some aspect the apparatus may also comprise a direct current (DC)power supply connectable in the series to the plurality of externalbatteries, and in use when the DC power supply is connected the DC powersupply is used as the power source.

In some aspects upon receiving a power capacity request from thecontroller each of the plurality of external batteries is capable ofdetermining an estimate of its own remaining capacity. The externalbatteries remaining capacity may be used to determine an estimate of thetotal external batteries remaining run time or state of charge. Thetotal external batteries remaining run time may be determined as afunction remaining run time of the power supplying external battery.

In some aspects the plurality of external batteries includes adownstream external battery and an upstream external battery, whereinthe upstream external battery is electrically connected to the powersource connection and the downstream external battery is electricallyconnected in the series to the upstream external battery. The upstreamexternal battery may be connected to the power source connection usingan electrical cable. Furthermore, one or more further external batteriesmay be electrically connected between the downstream external batteryand the upstream external battery.

In some aspects the upstream external battery is configured to send thedetermined estimate of the upstream external batteries remainingcapacity to the downstream external battery. Each of the one or morefurther external batteries may be configured to send the determinedestimate of the external battery remaining capacity along the series tothe downstream external battery. The downstream external battery may beconfigured to determine a total external battery remaining capacity orstate of charge from all the external batteries electrically connectedin the series. The downstream external battery may be configured todetermine the total external battery remaining run time from all theexternal batteries electrically connected in the series as a function ofa remaining run time of the upstream external battery being used toprovide the power to run the apparatus.

In some aspects upon receiving a remaining capacity request from thecontroller the internal battery may be capable of determining anestimate of the internal battery remaining power capacity. The internalbattery remaining capacity may be used to determine an estimate ofinternal battery remaining run time. The internal battery remaining runtime may be determined as a function of a remaining run time of theinternal battery when the internal battery is being used to provide thepower to run the apparatus or the power supplying external battery whenone of the plurality of external batteries is being used to run theapparatus.

In some aspects the controller may be configured to calculate anestimate of a total battery remaining capacity or total state of chargeof the plurality of external batteries and the internal batteries. Thecontroller may be configured to calculate an estimate of a total batteryremaining run time of the plurality of external batteries and theinternal batteries. In some aspects the user interface display may beconfigured to display the estimate of the total battery remainingcapacity, the total battery remaining charge and/or the estimate of thetotal battery remaining run time.

In some aspects the apparatus may be a ventilator.

An aspect of the present technology includes a method of determining anestimate of a total available battery capacity from two or more batterypower sources electrically connected to a respiratory device, therespiratory device comprising a controller configured to perform themethod of request an estimate of available capacity from a first batterypower source to provide a first battery capacity level, request anestimate of available capacity from a second battery power source toprovide a second battery capacity level, and combine the first batterycapacity level and the second battery capacity level to determine anestimate of the total available battery capacity.

In some aspects the total available battery capacity is an estimate of atotal remaining capacity or a total remaining charge or a total state ofcharge from the first battery source and the second battery source.

In some aspects the first battery source is at least one externalbattery electrically connected to the respiratory device and the secondbattery source is an internal battery located within the respiratorydevice. The first battery source may include a plurality of externalbatteries connected in series, each of the plurality of externalbatteries including an input port and output port configured to receivean electrical cable therebetween. The plurality of external batteriesmay include a downstream external battery, the output port of thedownstream external battery is electrically coupled to the respiratorydevice via an electrical cable and the input port of the downstreamexternal battery is electrically coupled via an electrical cable to theoutput port of a second external battery of the plurality of externalbatteries. Furthermore, each of the plurality of external batteries maybe electrically coupled to an adjacent external battery via anelectrical cable connected between the input port of one of theplurality of external batteries and the output port of the adjacentexternal battery. The method may further include each external batteryproviding an estimate of available capacity and sending the availablecapacity via the electrical cables along the series to the upstreamexternal battery. The method may also include displaying the totalavailable battery capacity on a user interface display of therespiratory device.

Another aspect of one form of the present technology is a respiratorydevice having improved power efficiency.

Another aspect of one form of the present technology is a respiratorydevice to provide a supply of breathable gas to a patient breathing insuccessive cycles, each cycle including an inspiration phase and anexpiration phase, the respiratory device comprising a blower including amotor configured to accelerate to reach an inspiration pressure providedduring the inspiration phase and decelerate to reach an expirationpressure provided during the expiration phase; a first power sourcearranged to supply power to run the motor of the blower; and an energystorage unit configured to store energy generated by the motor when themotor decelerates; wherein when a voltage present in the energy storageunit exceeds a first threshold, the supply of power from the first powersource to the motor is turned off and the motor is energized by theenergy in the energy storage unit and when the voltage in the energystorage unit falls below a second threshold the supply of power from thefirst power source to the motor is turned on.

In some aspects the energy storage unit includes at least one capacitoror super capacitor. In some aspects the respiratory device furthercomprises a regulator switch that monitors the voltage of the energystorage unit and switches the supply of power to the motor from thefirst power source on and off.

Of course, portions of the aspects may form sub-aspects of the presenttechnology. Also, various ones of the sub-aspects and/or aspects may becombined in various manners and also constitute additional aspects orsub-aspects of the present technology.

Other features of the technology will be apparent from consideration ofthe information contained in the following detailed description,abstract, drawings and claims.

5 BRIEF DESCRIPTION OF THE SEVERAL VIEWS OF THE DRAWINGS

The present technology is illustrated by way of example, and not by wayof limitation, in the figures of the accompanying drawings, in whichlike reference numerals refer to similar elements including:

5.1 Treatment Systems

FIG. 1 shows a system in accordance with the present technology. Apatient 1000 wearing a patient interface 3000, receives a supply of airat positive pressure from a device or ventilator 4000. Air from thedevice is humidified in a humidifier 5000, and passes along an aircircuit 4170 to the patient 1000. In an alternative arrangement (notshown) the humidifier may be located upstream or before the device orventilator 4000.

5.2 Therapy

5.2.1 Respiratory System

FIG. 2a shows an overview of a human respiratory system including thenasal and oral cavities, the larynx, vocal folds, oesophagus, trachea,bronchus, lung, alveolar sacs, heart and diaphragm.

FIG. 2b shows a view of a human upper airway including the nasal cavity,nasal bone, lateral nasal cartilage, greater alar cartilage, nostril,lip superior, lip inferior, larynx, hard palate, soft palate,oropharynx, tongue, epiglottis, vocal folds, oesophagus and trachea.

5.3 Patient Interface

FIG. 3a shows an example patient interface in accordance with one formof the present technology.

5.4 Ventilator Device

FIG. 4a shows a perspective view of a ventilator device in accordancewith one form of the present technology.

FIG. 4b shows a front view of the ventilator device of FIG. 4a

FIG. 4c shows a rear view of the ventilator device of FIG. 4 a.

FIG. 4d shows a bottom view of the ventilator device of FIG. 4 a.

FIG. 4e shows a schematic of the arrangement of internal components in aventilator according to an aspect of the present technology.

FIG. 4f shows a schematic view of the internals of the pneumatic blockaccording to an aspect of the present technology.

FIG. 4g shows a schematic diagram of the pneumatic circuit of a devicein accordance with one form of the present technology. The directions ofupstream and downstream are indicated.

FIG. 4h shows a schematic diagram of the electrical components of adevice in accordance with one aspect of the present technology.

FIG. 4i shows a schematic diagram of the algorithms implemented in adevice in accordance with an aspect of the present technology. In thisfigure, arrows with solid lines indicate an actual flow of information,for example via an electronic signal.

FIG. 4j shows a schematic diagram of the power arrangements for aventilator provided with AC power according to an aspect of the presenttechnology.

FIG. 4k shows a schematic diagram of the power arrangements forrecharging external batteries for a ventilator provided with AC powerindependent of the ventilator according to an aspect of the presenttechnology.

FIG. 4l shows a schematic diagram of the power arrangements for aventilator provided with external battery power according to an aspectof the present technology.

FIG. 4m shows a schematic diagram of the power arrangements for aventilator provided with DC power according to an aspect of the presenttechnology.

FIG. 4n shows a schematic of a power regeneration circuit according toan aspect of the present technology.

FIG. 4o shows a schematic of a power regeneration circuit including avoltage regulator boost according to another aspect of the presenttechnology.

FIG. 4p is a schematic diagram of a hardware alarm controller controlsystem according to another form or example of the present technology.

5.5 Humidifier

FIG. 5 shows a schematic of a humidifier in accordance with one aspectof the present technology.

5.6 Breathing Waveforms

FIG. 6a shows a model typical breath waveform of a person whilesleeping. The horizontal axis is time, and the vertical axis isrespiratory flow. While the parameter values may vary, a typical breathmay have the following approximate values: tidal volume, Vt, 0.5 L,inhalation time, Ti, 1.6 s, peak inspiratory flow, Qpeak, 0.4 L/s,exhalation time, Te, 2.4 s, peak expiratory flow, Qpeak, −0.5 L/s. Thetotal duration of the breath, Ttot, is about 4 s. The person typicallybreathes at a rate of about 15 breaths per minute (BPM), withVentilation, Vent, about 7.5 L/minute. A typical duty cycle, the ratioof Ti to Ttot is about 40%.

6 DETAILED DESCRIPTION OF EXAMPLES OF THE TECHNOLOGY

Before the present technology is described in further detail, it is tobe understood that the technology is not limited to the particularexamples described herein, which may vary. It is also to be understoodthat the terminology used in this disclosure is for the purpose ofdescribing only the particular examples discussed herein, and is notintended to be limiting.

6.1 Treatment Systems

In one form, the present technology comprises apparatus for treating arespiratory disorder. The apparatus may comprise a flow generator orblower for supplying pressurised respiratory gas, such as air, to thepatient 1000 via an air delivery tube 4170 leading to a patientinterface 3000.

6.2 Therapy

In one form, the present technology comprises a method for treating arespiratory disorder comprising the step of applying positive pressureto the entrance of the airways of a patient 1000. In another form of thepresent technology comprises a method for treating a respiratorydisorder comprising the step of applying positive pressure to provideinvasive ventilation to an intubated patient. In another form of thepresent technology provides a method for treating a respiratory disordercomprising the step of providing a pressure-cycled or volume-cycledtherapy

6.3 Patient Interface 3000

A non-invasive patient interface 3000 in accordance with one aspect ofthe present technology comprises the following functional aspects: aseal-forming structure 3100, a plenum chamber 3200, a positioning andstabilising structure 3300 and a connection port 3600 for connection toair circuit 4170.

In one form of the present technology, a seal-forming structure 3100provides a sealing-forming surface, and may additionally provide acushioning function. A seal-forming structure 3100 in accordance withthe present technology may be constructed from a soft, flexible,resilient material such as silicone.

In one form the seal-forming portion of the non-invasive patientinterface 3000 comprises a pair of nasal puffs, or nasal pillows, eachnasal puff or nasal pillow being constructed and arranged to form a sealwith a respective naris of the nose of a patient.

In one form the non-invasive patient interface 3000 comprises aseal-forming portion that forms a seal in use on an upper lip region(that is, the lip superior) of the patient's face.

In one form the non-invasive patient interface 3000 comprises aseal-forming portion that forms a seal in use on a chin-region of thepatient's face.

In some forms a functional aspect may be provided by one or morephysical components. In some forms, one physical component may provideone or more functional aspects. In use the seal-forming structure 3100is arranged to surround an entrance to the airways of the patient so asto facilitate the supply of air at positive pressure to the airways.Preferably the plenum chamber 3200 has a perimeter that is shaped to becomplementary to the surface contour of the face of an average person inthe region where a seal will form in use. In use, a marginal edge of theplenum chamber 3200 is positioned in close proximity to an adjacentsurface of the face. Actual contact with the face is provided by theseal-forming structure 3100. Preferably the seal-forming structure 3100extends in use about the entire perimeter of the plenum chamber 3200.

Preferably the seal-forming portion 3100 of the patient interface 3000of the present technology is held in sealing position in use by thepositioning and stabilising structure 3300, such as headgear.

In one form, the patient interface 3000 includes a vent 3400 constructedand arranged to allow for the washout of exhaled carbon dioxide. Oneform of vent 3400 in accordance with the present technology comprises aplurality of holes, for example, about 20 to about 80 holes, or about 40to about 60 holes, or about 45 to about 55 holes. Preferably the vent3400 is located in the plenum chamber 3200. In one form the patientinterface 3000 may also include at least one decoupling structure 3500,for example a swivel or a ball and socket. The vent 3400 may be locatedin the decoupling structure 3500. Connection port 3600 allows forconnection to the air circuit 4170.

The patient interface 3000 may further include a forehead support 3700.The patient interface may also include an anti-asphyxia valve.

In one form of the present technology, a patient interface 3000 includesone or more ports that allow access to the volume within the plenumchamber 3200. In one form this allows a clinician to supply supplementaloxygen. In one form this allows for the direct measurement of a propertyof gases within the plenum chamber 3200, such as the pressure.

6.4 Device 4000

A ventilator device 4000 in accordance with one form of the presenttechnology is shown in FIGS. 4a to 4e . The ventilator 4000 includes ahousing 4012, an expiration air inlet port 4014 and an inspirationoutlet port 4016. The ports 4014 and 4016 are connectable to tubes (notshown) which may be inserted into the trachea of a patient, to a face ornasal mask that fits over the nose or mouth or both of a patient, orotherwise attaches to the patient to assist with breathing. The housingfor the ventilator may be portable and include a handle 4018 forcarrying the ventilator. The housing may have an upper housing case4020, a chassis 4021 and a lower housing case 4022 that are coupledtogether to form the external faces of the ventilator. However, it is tobe understood that the housing may have other configurations such asonly comprising two component parts with an upper and lower casing ormay have more than three component parts. The ventilator may include aventilator or aspects of a ventilator as described the Assigneesco-pending U.S. patent application Ser. No. 13/624,167 filed 21 Sep.2012 and incorporated herein in its entirety.

The chassis 4021 may provide the structural skeleton for the ventilatorassembly. The chassis 4021 may be structured to receive an inlet filterassembly 4036 and inlet seal 4038 respectively described in more detailbelow. The inlet seal 4038 is also configured to couple to an inlet of apneumatic block module 4056. Preferably the inlet seal 38 is formed of acompliant material such as silicone, the inlet seal may be over mouldedonto the inlet of the pneumatic block module 4056.

The chassis 4021 may also comprise a pneumatic block seat into which thepneumatic block module 4056 is located for ease of alignment andassembly of the pneumatic block module 4056 within the housing. Thechassis 4021 also may include a portion of the handle 4018.

The rear of the chassis 4021 may include a range of interfaces for avariety of connections and switches on the rear panel. For example,interfaces for electrical connectors 4049, switches 4051, dataconnections 4047 and oxygen connections 4046.

The chassis 4021 may also provide a number of interfaces to locate andretain components of the ventilator 4000 such as a cooling fan 4068, PCB4086, and components of an expiratory portion 4031 that is locatedadjacent the expiration air inlet port 4014 (see FIG. 4e ).

The expiratory portion 4031 of the ventilator 4000 is configured toallow the insertion of an expiratory interface module to receive theexpired gas from the patient, via the expiration air inlet port 4014.The different expiratory interface modules may include an expiratoryvalve and an expiratory adaptor.

As seen in FIGS. 4a to 4e the ventilator 4000 may include a batterycompartment to locate and interface with a removable internal battery4450. A removable battery cover 4052 is provided on the outer bottomsurface of the lower housing 4022 to allow access to insert or removethe battery. A removable expiratory cover 4048, an oxygen sensor cover4054 and grills 4044 to allow component heat venting are also providedon the outer bottom surface as seen in FIG. 4d . The lower housing 4022may also include an anti-slip foot or grip surface or one or moreanti-slip or grip feet 4053, such as a thermoplastic polyurethane (TPU)foot, on the outer bottom surface to prevent the ventilator 4000 fromslipping off a smooth surface. The anti-slip or grip feet 4053 may alsoraise the ventilator 4000 to prevent spilt water from pooling under thebottom of the ventilator. A portion of the handle 4018 is also locatedwithin the lower housing case 4022.

As seen in FIG. 4a the upper housing case 4020 provides the top face ofthe ventilator 4000 and is structured to receive a user interfacedisplay device 4024. The housing may include a computer or processordriven user interface display device 4024, such as a liquid crystaldisplay (LCD) adapted to receive touch inputs for the computer. Thedisplay device may be flush with a top surface of the housing to beeasily visible while the ventilator is in use. An alarm indicator lightbar 4026, such as a light emitting diode (LED) light bar, and a button4028 for disabling an audio or visual alarm may be adjacent the display.However it is to be understood that other known user interface systemsmay be used such as screens, buttons, dial, keys or combinationsthereof. The chassis 4021, lower housing case 4022 and upper housingcase 4020 are coupled together for assembly of the complete ventilatorhousing 4012. Fasteners such as screws may be used to assembly thehousing 4012 although any other known fasteners may also be used. Thechassis 4021 is assembled between the upper housing case 4020 and thelower housing case 4022.

As shown in FIG. 4c , the rear of the housing 4012 may include a filterassembly 4036. Air to be pumped into the lungs of the patient is drawninto the air inlet associated with the filter assembly. The air passesthrough a permeable filter membrane in the filter and enters an airpassage for air flowing to the patient.

The rear of the housing may include data connections 4047 forcommunications with digital devices such as computer networks, alarmsystems, a pulse oximeter (e.g., spO2) and digital recording media. Anelectrical power connection 4049 and an on-off switch 4051 may also bepositioned at the rear of the housing. An input grill 4044-I provides aninlet for air to cool components and permit dissipation of the heatgenerated by operation of the internal components (e.g., blower motorsand CPU). Movement of the heated air across internal components may bedriven by a cooling fan 4068 in the housing, which may be near a heatedair output grill 4044-O (shown on bottom of housing in FIG. 4d ). Inaddition, an oxygen (O₂) inlet port 4046 may be at the rear of thehousing, which permits coupling with an oxygen source.

FIG. 4d shows a bottom of the ventilator 4000. The removable expiratorycover 4048, which serves as an external access hatch, provides access toand protection for the compartment of the expiratory portion or sectionof the housing. Removing the expiratory cover 4048 provides access toany inserted expiratory gas routing module as well as the expiration airinlet port 4014. It also allows for easy removal and replacement of theexpiratory gas routing module such as an expiratory valve or expiratoryadapter. The expiratory cover 4048 may be tightened to the housing toreduce excess play by a latch 4050 that may be turned with the fingers.Optionally, in some embodiments, the latch might serve to lock the latchfrom releasing. An optional latch release button 4050R may be operatedto disengage the expiratory cover. The release button 4050R may bedepressed to unlatch the expiratory cover 4048. A skilled addresseewould understand that alternative ways of removably securing andcoupling the expiratory cover 4048 to the housing may also be utilized.The bottom of the ventilator housing may also have removable batterycover 4052 for a replaceable internal battery and an oxygen sensor cover4054 which may be removed to access an oxygen sensor 4047.

FIG. 4e shows the internal components of the ventilator 4000 accordingto an aspect of the present technology. The ventilator 4000 may includesome or all of the following components: an inlet filter 4034, inletseal 4038, inlet muffler 4039, an oxygen supply path 4043, a pneumaticblock module 4056, an inspiratory portion 4033, safety valve 4085, anexpiratory portion 4031, PCB and controls 4086, cooling fan 4068 andinternal battery 4450.

The pneumatic block module 4056 is arranged within the ventilator suchthat its air passages are aligned with the filter assembly 4036 at theair inlet 4034, the inspiration outlet port 4016 and the oxygen supplypath 4043. Arrows indicate the path of the air flow 4035 and the oxygenflow 4045 respectively through the ventilator 4000. The air flow 4035enters via the air inlet 4034 and travels through the filter assembly4036 and inlet seal 4038 into an inlet muffler 4039 of the pneumaticblock module 4056. Optionally an oxygen source may be attached at theoxygen inlet port 4046 and the oxygen flow 4045 is directed through theoxygen supply path 4043 and an oxygen seal into the pneumatic blockmodule 4056 where it is combined with the inlet air flow 4035 within theinlet muffler 4039. Within the pneumatic block module 4056 the air flow4035 is pressurized by a main blower 4104 (see FIG. 40. The pressurizedair/oxygen flow 4035, 4045 are directed out of the pneumatic blockmodule 4056 via outlet muffler 4084 and through the main seal 4040 intothe inspiratory portion 4033 and then out the inspiration outlet port4016 to be delivered to the patient interface (not shown) via an airdelivery conduit (not shown).

An oxygen sensor 4064, which may be located in an oxygen sensorcompartment of the inspiratory portion 4033, measures the amount ofoxygen being delivered to patient. The oxygen sensor 4064 may be mountedin the housing 4012 such that it is easily replaced and adjacent theinspiration outlet port 4016. The oxygen sensor detects the oxygen levelof the air being pumped to the patient. Data from the oxygen sensor maybe used to trigger alarms related to oxygen concentration and to providedata to the microprocessor to display the oxygen concentration on theuser interface. The amount of oxygen supplied may be controlled byadjusting the known volumes of air and oxygen supplied to the patient.However, the oxygen sensor may also optionally be used to regulate theamount of supplemental oxygen to be supplied through the oxygen inletport 4046.

An oxygen sensor cover 4054 (shown in FIG. 4d ) on the bottom of thehousing is removable to provide access to the oxygen sensor containedwithin an oxygen sensor compartment of the housing. The oxygen sensorfits in a mount within the housing and adjacent to the inspirationoutlet port 4016. A portion of the air flowing through the inspirationoutlet port 4016 is sensed by the oxygen sensor. The sensor generatesdata signals indicating the oxygen level of the gas. The data isconveyed to a data connection which conveys the data to a processor. Theprocessor analyzes the data to determine the amount of supplementaloxygen to be added to the air being pumped to the patient.

The oxygen source may be a low pressure oxygen supply or a high pressureoxygen supply. For the supply of a high pressure oxygen source an oxygenregulator (not shown) may be located within the oxygen supply path 4043to reduce the pressure from the high pressure oxygen source before theoxygen enters the inlet muffler 4039. The oxygen inlet port 4046 may beadapted to couple to a range of different oxygen connection adaptors toallow the connection of different types of oxygen connectors used indifferent jurisdictions including but not limited to male or femalediameter index safety system (DISS), sleeve indexing system (SIS),National Institute of Standards Technology (NIST) and AssociationFrancaise De Normalisation (AFNOR).

In an alternative arrangement (not shown) a high pressure oxygen sourcemay be provided after the main blower 4104 such as within the outletmuffler 4084 where it is mixed with the pressurized air source. In someexamples the high pressure oxygen may be used to provide the pressuresource for the gas flow to the patient. In some arrangements lowpressure oxygen may optionally be provided to the air circuit 4170 orthe patient interface 3000.

Although the pneumatic block module 4056 is schematically shown as arectangular shape it is to be understood that the pneumatic block module4056 may have any shape including a non-symmetrical shape that conformsto a seat in the housing and would minimize the possibility that thepneumatic block module 4056 is improperly inserted into the housing.

The main printed circuit board (PCB) 4086, may be assembled and mountedto the chassis 4021 and located between the chassis 4021 and the lowerhousing case 4022. The electronic components of the main board mayinclude a processor, electrical connectors to convey data signals fromthe pneumatic block module 4056 such as an electrical power and dataconnector for the blower which provides pressurized air to theinspiration outlet port 4016. In this regard, the electrical connectorsprovide power and signal paths between the electronic components on aPCB in the pneumatic block module 4056 and the electronic components onthe main PCB in the housing. The electronic components of the main boardmay also include a data and power connector for any sensors, such as theoxygen sensor 4064. The electronic components in the housing may controla generation of images for the display device, sound signals for aspeaker 4061, such as for producing audible alarms, detect signals frompressure and oxygen sensors, and control the rotational speed of theblower. The ventilator 400 may optional include a clock connected to thePCB 4086.

The chassis 4021 may include a plurality of mounting seats orcompartments configured to receive different components of theventilator 4000, such as a pneumatic block mounting seat that mayconform to the perimeter of the pneumatic block module 4056, a filterseat and/or a compartment for the inlet filter assembly 4036, and othermounting seats for the low pressure oxygen connection assembly, acooling fan 4068, and deformable seals. The chassis 4021 may alsoinclude embedded or integrated air passages and ports that may be moldedwithin the chassis structure such as for conveying air between sectionsor compartments of the chassis. For example, air at a known pressure maybe channelled through passages of the chassis from the pneumatic blockmodule to the PEEP air supply.

FIG. 4f is a schematic of the internal components of the pneumatic blockmodule 4056. The pneumatic block module 4056 includes the main blower4104 with volute assembly 4108, an inlet non-return valve assembly 4114,an optional oxygen inlet port 4144, a positive end expiratory pressure(PEEP) blower 4124, outlet muffler 4084, safety valve 4085, pressuresensor 4128, flow sensor 4130 and flow element 4132 and a PEEP pressuresensor 4142. The volute assembly 4108 forms the majority of the air pathand performs some of the critical functions of the pneumatic blockmodule 4056.

The pneumatic block 4056 may include electrovalve 4116 and a flowcontrol electrovalve 4120 that are configured to communicate with andcontrol the non-return valve assembly 4114. A PEEP electrovalve 4136 isconfigured to communicate with the PEEP blower 4124 to control thesupply of the pressure from the PEEP blower 4124 to the expiratoryportion 4031. A PEEP pressure tube is coupled between the PEEPexpiratory valve and a PEEP supply port in the expiratory portion 4031to provide the PEEP pressure source. The PEEP pressure sensor 4142senses the PEEP pressure.

FIG. 4g shows a schematic arrangement for another form of a device 4000.The pneumatic path of the device 4000 preferably comprises an inlet airfilter 4034, an inlet muffler 4039, a controllable source pressuredevice 4140 capable of supplying air at positive pressure (preferably amain blower 4104), and an outlet muffler 4084. One or more transducersor sensors 4270, such as pressure sensors 4128 and flow sensors 4130 areincluded in the pneumatic path.

The preferred pneumatic block 4056 comprises a portion of the pneumaticpath that is located within the external housing 4012.

The device 4000 preferably has an electrical power supply 4210, one ormore input devices 4220, a central controller 4230, a pneumaticcontroller 4240, a therapy device 4245, one or more protection circuits4250, memory 4260, transducers 4270, data communication interface 4280and one or more output devices 4290. Electrical components 4200 may bemounted on a single Printed Circuit Board Assembly (PCBA). In analternative form, the device 4000 may include more than one PCBA.

The central controller 4230 of the device 4000 is programmed to executea set 4300 of one or more algorithm modules in use, preferably includinga pre-processing transducer signals module 4310, a therapy engine module4320, a pressure control module 4330, and further preferably a faultcondition module 4340.

6.4.1 Device Mechanical & Pneumatic Components

6.4.1.1 Air Filter(s) 4110

A device in accordance with one form of the present technology mayinclude an air filter 4110, or a plurality of air filters 4110.

In one form, an inlet air filter 4034 is located at the beginning of thepneumatic path upstream of a blower 4104. See FIG. 4 g.

In one form, an outlet air filter 4150, for example an antibacterialfilter, is located between an outlet of the pneumatic block 4056 and apatient interface 3000. See FIG. 4 g.

6.4.1.2 Muffler(s) 4120

In one form of the present technology, an inlet muffler 4039 is locatedin the pneumatic path upstream of a blower 4104. See FIG. 4 g.

In one form of the present technology, an outlet muffler 4084 is locatedin the pneumatic path between the blower 4104 and a patient interface3000. See FIG. 4 g.

6.4.1.3 Pressure Device 4140

In a preferred form of the present technology, a pressure device 4140for producing a flow of air at positive pressure is a controllable mainblower 4104. For example the main blower may include a brushless DCmotor 4404 a with one or more impellers housed in a volute. The blowermay be preferably capable of delivering a supply of air, for examplebetween about 10 litres/minute and about 120 litres/minute, at apositive pressure in a range from about 3 cmH₂O to about 40 cmH₂O, or inother forms up to about 60 cmH₂O.

The pressure device 4140 is under the control of the pneumaticcontroller 4240.

6.4.1.4 Transducer(s) 4270

In one form of the present technology, one or more transducers orsensors 4270 are located upstream of the pressure device 4140. The oneor more transducers 4270 are constructed and arranged to measureproperties of the air at that point in the pneumatic path.

In one form of the present technology, one or more transducers 4270 arelocated downstream of the pressure device 4140, and upstream of the aircircuit 4170. The one or more transducers 4270 are constructed andarranged to measure properties of the air at that point in the pneumaticpath.

In one form of the present technology, one or more transducers 4270 arelocated proximate to the patient interface 3000. The one or moretransducers 4270 may include for example pressure, flow, speed or oxygensensors.

6.4.1.5 Anti-Spill Back Valve 4160

In one form of the present technology, an anti-spill back valve islocated between an optional humidifier 5000 and the device 4000. Theanti-spill back valve is constructed and arranged to reduce the riskthat water will flow upstream from the humidifier 5000, for example tothe motor 4104.

6.4.1.6 Air Circuit 4170

An air circuit 4170 in accordance with an aspect of the presenttechnology is constructed and arranged to allow a flow of air orbreathable gasses between an outlet of the device 4000, such as theinspiration air outlet port 4016, and the patient interface 3000. Theair delivery circuit 4170 may include a single limb circuit or a doublelimb circuit. A double limb circuit includes an expiratory conduit fordelivery of the patient's expired gas back to the ventilator and out anexhaust port. The exhaust port may include a filter such as ananti-bacterial filter

6.4.1.7 Oxygen Delivery 4180

In one form of the present technology, supplemental oxygen 4180 isdelivered to a point in the pneumatic path.

In one form of the present technology, supplemental oxygen 4180 isdelivered upstream of the pneumatic block 4056.

In one form of the present technology, supplemental oxygen 4180 isdelivered to the air circuit 4170.

In one form of the present technology, supplemental oxygen 4180 isdelivered to the patient interface 3000.

6.4.2 Device Electrical Components 4200

6.4.2.1 Power Supply 4210

Power supply 4210 supplies power to the other components of the basicdevice 4000: the input device 4220, the central controller 4230, thetherapy device 4245, and the output device 4290.

In one form of the present technology, the power supply 4210 may includean internal power supply, such as an internal battery 4450 (see FIG. 4j) that may be removably located within the external housing 4012 of thedevice 4000. The internal battery 4450 may be a lithium-ion battery andmay be configured to provide 4-12 hours of use, for example up to 4, 5,6, 7 or 8 hours of continuous use. The internal battery 4450 may providea voltage in the range of 10-18 volts direct current (DC) power, such as12-16.8 volts DC power and have a capacity of 90-100 Watts (W) per hour(hr), such as approximately 95 Watts per hour.

In another form of the present technology, power supply 4210 mayalternatively or additionally include one or more external powersupplies, such as external batteries 4410, 4420, configured to connectvia an electrical cord to a power source connection of the device 4000(see FIGS. 4j-4m ). A plurality of external batteries may be connectedin series to the device or ventilator 4000, for example 2, 3, 4 or moreexternal batteries may be connected in series to the device 4000. Theexternal batteries 4410, 4420 may be connected to the device orventilator 4000 and each other via electrical cables, such as DC cableor power cords 4462. FIGS. 4l to 4m show a downstream external battery4410 and an upstream external battery 4420 connected in series to theventilator 4000. It is to be understood that further external batteries(not shown) may be connected in series between the downstream externalbattery 4410 and the upstream external battery 4420 to extend theavailable external battery power.

Each external battery includes an input port and output port to allowconnection of cables for communication of power and signals along theseries. Each of the external batteries 4410, 4420 may be the same ordifferent, i.e. be capable of providing the same amount of power ordifferent amounts of power respectively. An external battery may providepower for 2-12 hours of use, such as up to 4, 5, 6, 7 or 8 hours ofcontinuous use. An external battery 4410, 4420 may provide a voltage inthe range of 10-30 volts direct current (DC) power, such as 24-26 voltsDC power and have a capacity of 90-100 Watts (W) per hour (hr), such asapproximately 95, 96, 97 Watts per hour.

In another arrangement the power supply 4210 allows connection to anAlternating Current (AC) power source via an AC power Supply unit (PSU)4430 (see FIG. 4j ). The AC PSU 4430 may be a switched mode power supplythat may provide universal input in a range of between 80-270 volts ACor between 100-240 volts AC. The AC PSU 4430 may provide a power outputof 60-100 Watts (W), such as approximately 90 W and a power supply ofapproximately 24 volts DC power. The AC PSU 4430 may be suitable for useon an aircraft. The AC PSU 4430 may be electrically connected to thepower source connection of the ventilator or device 4000 directly (i.e.no external batteries are connected to the ventilator 4000, not shown)or in series upstream from one or external batteries 4410, 4420 that areelectrically connected to the ventilator 4000 as shown in FIG. 4 j.

In a further arrangement shown in FIG. 4m , the power supply 4210 mayallow connection to a DC mains power supply 4460 via a DC mains powercord 4462. The DC mains power supply may provide approximately 12-24volts of power. The DC mains power cord 4462 may electrically connectbetween the power source connection of the ventilator or device 4000 andthe DC mains power supply 4460 without any intervening externalbatteries (not shown). Alternatively, as shown in FIG. 4m , one or moreof the upstream external battery 4420 and the downstream externalbattery 4410 may also be connected in series between the ventilator 4000and the DC mains power. In one arrangement the external batteries 4410,4420, if connected, will not be charged by the DC power supply when thedevice is in use. However, alternatively the DC mains power may be usedto charge the external batteries 4410, 4420 depending upon the powerusage requirements of the device 4000 and the available power beingsupplied by the DC mains power 4460. The internal battery 4450 may alsobe present in ventilator 4000 and may optionally be charged by the DCmains power 4460.

It is to be understood that the above power capacity ranges areexemplary only and the AC PSU 4430, the internal battery 4450, and theexternal batteries 4410, 4420 may have different power capacity andoutputs to those described above. The power management of the device4000 is described in more detail below.

6.4.2.1.1 Input Device(s) 4220

Input devices 4220 comprises buttons, switches or dials to allow aperson to interact with the device 4000. The buttons, switches or dialsmay be physical devices, or software devices accessible via a touchscreen. The buttons, switches or dials may, in one form, be physicallyconnected to the external housing 4012, or may, in another form, be inwireless communication with a receiver that is in electrical connectionto the central controller 4230.

In one form the input device 4220 may be constructed and arranged toallow a person to select a value and/or a menu option.

6.4.2.1.2 Central Controller 4230

In one form of the present technology, the central controller orProcessor 4230 is a dedicated electronic circuit configured to receiveinput signal(s) from the input device 4220, and to provide outputsignal(s) to the output device 4290 and/or the therapy device controller4245.

In one form, the central controller 4230 is an application-specificintegrated circuit. In another form, the central controller 4230comprises discrete electronic components.

The processor 4230 is configured to receive input signal(s) from one ormore transducers 4270, and one or more input devices 4220.

The processor 4230 is configured to provide output signal(s) to one ormore of an output device 4290, a pneumatic controller 4240, a datacommunication interface 4280 and humidifier controller 5250.

In some forms of the present technology, the processor 4230, or multiplesuch processors, is configured to implement the one or moremethodologies described herein such as the one or more algorithms 4300expressed as computer programs stored in a non-transitory computerreadable storage medium, such as memory 4260. In some cases, aspreviously discussed, such processor(s) may be integrated with a device4000. However, in some forms of the present technology the processor(s)may be implemented discretely from the pressure generation components ofthe device 4000, such as for purpose of performing any of themethodologies described herein without directly controlling delivery ofa respiratory treatment. For example, such a processor may perform anyof the methodologies described herein for purposes of determiningcontrol settings for a ventilator or other respiratory related events byanalysis of stored data such as from any of the sensors describedherein.

6.4.2.1.3 Therapy Device 4245

In one form of the present technology, the therapy device 4245 isconfigured to deliver therapy to a patient 1000 under the control of thecentral controller 4230.

6.4.2.1.4 Output Device 4290

An output device 4290 in accordance with the present technology may takethe form of one or more of a visual, audio, and haptic output. A visualoutput may be a Liquid Crystal Display (LCD) or Light Emitting Diode(LED) display. An audio output may be a speaker or audio tone emitter.

6.4.2.1.5 Clock 4232

Preferably device 4000 includes a clock 4232 that is connected toprocessor 4230.

6.4.2.1.6 Pneumatic Controller 4240

In one form of the present technology, the pneumatic controller 4240 isa pressure control module 4330 that forms part of the algorithms 4300executed by the processor 4230.

In one form of the present technology, pneumatic controller 4240 is adedicated motor control integrated circuit.

In one form of the present technology, pneumatic controller 4240 is apneumatic block processor 4630.

6.4.2.1.7 Protection Circuits 4250

Preferably a device 4000 in accordance with the present technologycomprises one or more protection circuits 4250.

One form of protection circuit 4250 in accordance with the presenttechnology is pneumatic block safety circuit 4632.

One form of protection circuit 4250 in accordance with the presenttechnology is an electrical protection circuit.

One form of protection circuit 4250 in accordance with the presenttechnology is a temperature or pressure safety circuit.

One form of protection circuit 4250 in accordance with the presenttechnology is an alarm controller. The alarm controller may be ahardware alarm controller 4610 as described in more detail below.

6.4.2.1.8 Memory 4260

In accordance with one form of the present technology the device 4000includes memory 4260, preferably non-volatile memory. In some forms,memory 4260 may include battery powered static RAM. In some forms,memory 4260 may include volatile RAM.

Preferably memory 4260 is located on PCBA. Memory 4260 may be in theform of EEPROM, or NAND flash.

Additionally or alternatively, device 4000 includes removable form ofmemory 4260, for example a memory card made in accordance with theSecure Digital (SD) standard.

In one form of the present technology, the memory 4260 acts as anon-transitory computer readable storage medium on which is storedcomputer program instructions expressing the one or more methodologiesdescribed herein, such as the one or more algorithms 4300.

6.4.2.1.9 Transducers 4270

Transducers may be internal of the device, or external of the device.External transducers may be located for example on or form part of theair delivery circuit, e.g. the patient interface. External transducersmay be in the form of non-contact sensors such as a Doppler radarmovement sensor that transmit or transfer data to the device.

6.4.2.1.9.1 Flow 4272

A flow transducer 4272 in accordance with the present technology may bebased on a differential pressure transducer, for example, an SDP600Series differential pressure transducer from SENSIRION or Zephyr™ flowsensors from HONEYWELL. The differential pressure transducer is in fluidcommunication with the pneumatic circuit, with one of each of thepressure transducers connected to respective first and second points ina flow restricting element.

In use, a signal representing total flow Qt from the flow transducer4272 is received by the processor 4230.

6.4.2.1.9.2 Pressure 4274

A pressure transducer 4274 in accordance with the present technology islocated in fluid communication with the pneumatic circuit. An example ofa suitable pressure transducer is a sensor from the HONEYWELL ASDXseries. An alternative suitable pressure transducer is a sensor from theNPA Series from GENERAL ELECTRIC. A further alternative suitablepressure transducer is a sensor from the series of TruStability™pressure sensors from HONEYWELL.

In use, a signal from the pressure transducer 4274 is received by theprocessor 4230. In one form, the signal from the pressure transducer4274 is filtered prior to being received by the processor 4230.

6.4.2.1.9.3 Motor Speed 4276

In one form of the present technology a motor speed signal 4276 isgenerated. A motor speed signal 4276 is preferably provided by pneumaticcontroller 4240. Motor speed may, for example, be generated by a speedsensor, such as a Hall effect sensor.

6.4.2.1.10 Data Communication Systems 4280

In one preferred form of the present technology, a data communicationinterface 4280 is provided, and is connected to processor 4230. Datacommunication interface 4280 is preferably connectable to remoteexternal communication network 4282. Data communication interface 4280is preferably connectable to local external communication network 4284.Preferably remote external communication network 4282 is connectable toremote external device 4286. Preferably local external communicationnetwork 4284 is connectable to local external device 4288.

In one form, data communication interface 4280 is part of processor4230. In another form, data communication interface 4280 is anintegrated circuit that is separate from processor 4230.

In one form, remote external communication network 4282 is the Internet.The data communication interface 4280 may use wired communication (e.g.via Ethernet, or optical fibre) or a wireless protocol to connect to theInternet.

In one form, local external communication network 4284 utilises one ormore communication standards, such as Bluetooth, or a consumer infraredprotocol.

In one form, remote external device 4286 is one or more computers, forexample a cluster of networked computers. In one form, remote externaldevice 4286 may be virtual computers, rather than physical computers. Ineither case, such remote external device 4286 may be accessible to anappropriately authorised person such as a clinician.

Preferably local external device 4288 is a personal computer, mobilephone, tablet or remote control.

6.4.2.1.11 Output Devices Including Optional Display, Alarms 4290

An output device 4290 in accordance with the present technology may takethe form of one or more of a visual, audio and haptic unit. A visualdisplay may be a Liquid Crystal Display (LCD) or Light Emitting Diode(LED) 4298 display. An audio display may be a buzzer 4296.

6.4.2.1.11.1 Display Driver 4292

A display driver 4292 receives as an input the characters, symbols, orimages intended for display on the display 4294, and converts them tocommands that cause the display 4294 to display those characters,symbols, or images.

6.4.2.1.11.2 Display 4294

A display 4294 is configured to visually display characters, symbols, orimages in response to commands received from the display driver 4292

6.4.3 Device Algorithms 4300

6.4.3.1 Pre-Processing Module 4310

As illustrated in FIG. 4i , a pre-processing module 4310 in accordancewith the present technology receives as an input, raw data from atransducer, for example a flow or pressure transducer, and preferablyperforms one or more process steps to calculate one or more outputvalues that will be used as an input to another module, for example atherapy engine module 4320.

In one form of the present technology, the output values include theinterface or mask pressure Pm, the respiratory flow Qr, and the leakflow Ql.

In various forms of the present technology, the pre-processing module4310 comprises one or more of the following algorithms: pressurecompensation 4312, vent flow 4314, leak flow 4316, respiratory flow4318, and jamming detection 4319.

6.4.3.1.1 Pressure Compensation 4312

In one form of the present technology, a pressure compensation algorithm4312 receives as an input a signal indicative of the pressure in thepneumatic path proximal to an outlet of the pneumatic block. Thepressure compensation algorithm 4312 estimates the pressure drop in theair circuit 4170 and provides as an output an estimated pressure, Pm, inthe patient interface 3000.

6.4.3.1.2 Vent Flow 4314

In one form of the present technology, a vent flow calculation algorithm4314 receives as an input an estimated pressure, Pm, in the patientinterface 3000 and estimates a vent flow of air, Qv, from a vent 3400 ina patient interface 3000.

6.4.3.1.3 Leak Flow 4316

In one form of the present technology, a leak flow algorithm 4316receives as an input a total flow, Qt, and a vent flow Qv, and providesas an output a leak flow Ql by calculating an average of Qt-Qv over aperiod sufficiently long to include several breathing cycles, e.g. about10 seconds.

In one form, the leak flow algorithm 4316 receives as an input a totalflow, Qt, a vent flow Qv, and an estimated pressure, Pm, in the patientinterface 3000, and provides as an output a leak flow Ql by calculatinga leak conductance, and determining a leak flow Ql to be a function ofleak conductance and pressure, Pm. Preferably leak conductance iscalculated as the quotient of low pass filtered non-vent flow Qt-Qv, andlow pass filtered square root of pressure Pm, where the low pass filtertime constant has a value sufficiently long to include several breathingcycles, e.g. about 10 seconds.

6.4.3.1.4 Respiratory Flow 4318

In one form of the present technology, a respiratory flow algorithm 4318receives as an input a total flow, Qt, a vent flow, Qv, and a leak flow,Ql, and estimates a respiratory flow of air, Qr, to the patient, bysubtracting the vent flow Qv and the leak flow Ql from the total flowQt.

6.4.3.2 Therapy Engine Module 4320

In one form of the present technology, a therapy engine module 4320receives as inputs one or more of a pressure, Pm, in a patient interface3000, and a respiratory flow of air to a patient, Qr, and provides as anoutput, one or more therapy parameters.

In one form of the present technology, a therapy parameter is atreatment pressure Pt.

In one form of the present technology, a therapy parameter is one ormore of a level of pressure support, and a target ventilation.

6.4.3.2.1 Phase Determination 4321

In one form of the present technology, a phase determination algorithm4321 receives as an input a signal indicative of respiratory flow, Qr,and provides as an output a phase of a breathing cycle of a patient1000.

In one form, the phase output is a discrete variable with values ofeither inhalation or exhalation.

In one form, the phase output is a discrete variable with values of oneof inhalation, mid-inspiratory pause, and exhalation.

In one form, the phase output is a continuous variable, for examplevarying from 0 to 1, or 0 to 2 Pi.

In one form, the phase output is determined to have a discrete value ofinhalation when a respiratory flow Qr has a positive value that exceedsa positive threshold. In one form, a phase is determined to have adiscrete value of exhalation when a respiratory flow Qr has a negativevalue that is more negative than a negative threshold.

6.4.3.2.2 Waveform Determination 4322

In one form of the present technology, a control module 4330 controls atherapy device 4245 to provide an approximately constant positive airwaypressure throughout a respiratory cycle of a patient.

In one form of the present technology, a control module 4330 controls atherapy device 4245 to provide positive airway pressure according to apredetermined waveform of pressure vs phase. In one form, the waveformis maintained at an approximately constant level for all values ofphase. In one form, the waveform is a square wave, having a higher valuefor some values of phase, and a lower level for other values of phase.

In one form of the present technology a waveform determination algorithm4322 receives as an input a value indicative of current patientventilation, Vent, and provides as an output a waveform of pressure vs.phase.

6.4.3.2.3 Ventilation Determination 4323

In one form of the present technology, a ventilation determinationalgorithm 4323 receives an input a respiratory flow Qr, and determines ameasure indicative of patient ventilation, Vent.

In one form ventilation determination algorithm 4323 determines acurrent value of patient ventilation, Vent, as the half the low-passfiltered absolute value of respiratory flow, Qr.

6.4.3.2.4 Determination of Inspiratory Flow Limitation 4324

In one form of the present technology, a processor executes one or morealgorithms for the detection of inspiratory flow limitation.

In one form the algorithm 4324 receives as an input a respiratory flowsignal Qr and provides as an output a metric of the extent to which theinspiratory portion of the breath exhibits inspiratory flow limitation.

In one form of the present technology, the inspiratory portion of eachbreath is identified by a zero-crossing detector. A number of evenlyspaced points (for example, sixty-five), representing points in time,are interpolated by an interpolator along the inspiratory flow-timecurve for each breath. The curve described by the points is then scaledby a scaler to have unity length (duration/period) and unity area toremove the effects of changing respiratory rate and depth. The scaledbreaths are then compared in a comparator with a pre-stored templaterepresenting a normal unobstructed breath, similar to the inspiratoryportion of the breath shown in FIG. 6a . Breaths deviating by more thana specified threshold (typically 1 scaled unit) at any time during theinspiration from this template, such as those due to coughs, sighs,swallows and hiccups, as determined by a test element, are rejected. Fornon-rejected data, a moving average of the first such scaled point iscalculated by processor 4230 for the preceding several inspiratoryevents. This is repeated over the same inspiratory events for the secondsuch point, and so on. Thus, for example, sixty five scaled data pointsare generated by processor 4230, and represent a moving average of thepreceding several inspiratory events, e.g. three events. The movingaverage of continuously updated values of the (e.g. sixty five) pointsare hereinafter called the “scaled flow”, designated as Qs(t).Alternatively, a single inspiratory event can be utilised rather than amoving average.

From the scaled flow, two shape factors relating to the determination ofpartial obstruction may be calculated.

Shape factor 1 is the ratio of the mean of the middle (e.g. thirty-two)scaled flow points to the mean overall (e.g. sixty-five) scaled flowpoints. Where this ratio is in excess of unity, the breath will be takento be normal. Where the ratio is unity or less, the breath will be takento be obstructed. A ratio of about 1.17 is taken as a threshold betweenpartially obstructed and unobstructed breathing, and equates to a degreeof obstruction that would permit maintenance of adequate oxygenation ina typical user.

Shape factor 2 is calculated as the RMS deviation from unit scaled flow,taken over the middle (e.g. thirty two) points. An RMS deviation ofabout 0.2 units is taken to be normal. An RMS deviation of zero is takento be a totally flow-limited breath. The closer the RMS deviation tozero, the breath will be taken to be more flow limited.

Shape factors 1 and 2 may be used as alternatives, or in combination. Inother forms of the present technology, the number of sampled points,breaths and middle points may differ from those described above.Furthermore, the threshold values can other than those described.

The above methods are exemplary and it is to be understood that othermethods of determining inspiratory flow limitation may also be used.

6.4.3.2.5 Determination of Apneas and Hypopneas 4325

In one form of the present technology, a processor 4230 executes one ormore algorithms for the determination of the presence of apneas and/orhypopneas.

Preferably the one or more algorithms receive as an input a respiratoryflow signal Qr and provide as an output a flag that indicates that anapnea or respectively an hypopnea has been detected.

In one form, an apnea will be said to have been detected when a functionof respiratory flow Qr falls below a flow threshold for a predeterminedperiod of time. The function may determine a peak flow, a relativelyshort-term mean flow, or a flow intermediate of relatively short-termmean and peak flow, for example an RMS flow. The flow threshold may be arelatively long-term measure of flow.

In one form, a hypopnea will be said to have been detected when afunction of respiratory flow Qr falls below a second flow threshold fora predetermined period of time. The function may determine a peak flow,a relatively short-term mean flow, or a flow intermediate of relativelyshort-term mean and peak flow, for example an RMS flow. The second flowthreshold may be a relatively long-term measure of flow. The second flowthreshold is greater than the flow threshold used to detect apneas.

The above methods are exemplary and it is to be understood that othermethods of determining the occurrence of apneas and/or hypopneas mayalso be used.

6.4.3.2.6 Determination of Snore 4326

In one form of the present technology, a processor 4230 executes one ormore snore algorithms for the detection of snore.

In one form the snore algorithm 4326 receives as an input a respiratoryflow signal Qr and provides as an output a metric of the extent to whichsnoring is present.

Preferably the algorithm 4326 comprises the step of determining theintensity of the flow signal in the range of 30-300 Hz. Furtherpreferably, algorithm 4326 comprises a step of filtering the respiratoryflow signal Qr to reduce background noise, e.g. the sound of airflow inthe system from the blower.

The above methods are exemplary and it is to be understood that othermethods of determining snore may also be used.

6.4.3.2.7 Determination of Airway Patency 4327

In one form of the present technology, a processor 4230 executes one ormore algorithms for the determination of airway patency.

In one form, airway patency algorithm 4327 receives as an input arespiratory flow signal Qr, and determines the power of the signal inthe frequency range of about 0.75 Hz and about 3 Hz. The presence of apeak in this frequency range is taken to indicate an open airway. Theabsence of a peak is taken to be an indication of a closed airway.

In one form, the frequency range within which the peak is sought is thefrequency of a small forced oscillation in the treatment pressure Pt. Inone implementation, the forced oscillation is of frequency 2 Hz withamplitude about 1 cmH₂O.

In one form, airway patency algorithm 4327 receives as an input arespiratory flow signal Qr, and determines the presence or absence of acardiogenic signal. The absence of a cardiogenic signal is taken to bean indication of a closed airway.

6.4.3.2.8 Determination of Treatment Pressure 4328

In one form of the present technology, processor 4230 executes one ormore algorithms 4328 for the determination of a target treatmentpressure Pt.

Preferably the algorithm 4328 receives as an input one of more of thefollowing:

i. A measure of respiratory phase;

ii. A waveform;

iii. A measure of ventilation;

iv. A measure of inspiratory flow limitation;

v. A measure of the presence of apnea and/or hypopnea;

vi. A measure of the presence of snore; and

vii. A measure of the patency of the airway.

Pi=phase(time), the phase may be discrete or continuous.

Phi=waveform function(Pi), this wave may include a square wave,sinusoidal or other wave shapes.

Integral controller Amplitude, A=G*Int(Vent−Vtgt)dt. Other forms ofcontroller may be used such as P, PI, PID.Pt(t)=A*Φ(Pi)+P0.

P0=“DC” component, may be constant, may be a function of indices ormeasures of one or more of flow limitation, apnea, hypopnea, patency,and snore.

(Note: In a basic CPAP mode A may be zero, in which case the overallpressure equation simplifies)

The algorithm 4328 determines the treatment pressure Pt as a function ofindices or measures of one or more of flow limitation, apnea, hypopnea,patency, and snore. In one implementation, these measures are determinedon a single breath basis, rather than on an aggregation of severalprevious breaths.

6.4.3.3 Control Module 4330

A control module 4330 in accordance with one aspect of the presenttechnology receives as an input a target treatment pressure Pt, andcontrols a therapy device 4245 to deliver that pressure.

A control module 4330 in accordance with one aspect of the presenttechnology receives as an input an EPAP pressure and an IPAP pressure,and controls a therapy device 4245 to deliver those respectivepressures.

6.4.3.4 Detection of Fault Conditions 4340

In one form of the present technology, a processor executes one or moremethods for the detection of fault conditions. Preferably the faultconditions detected by the one or more methods includes at least one ofthe following:

-   -   Power failure (no power, or insufficient power)    -   Transducer fault detection    -   Failure to detect the presence of a component    -   Operating parameters outside recommended ranges (e.g. pressure,        flow, temperature, PaO₂)    -   Failure of a test alarm to generate a detectable alarm signal.

Upon detection of the fault condition, the corresponding algorithmsignals the presence of the fault by one or more of the following:

-   -   Initiation of an audible, visual &/or kinetic (e.g. vibrating)        alarm    -   Sending a message to an external device    -   Logging of the incident        6.4.3.5 Therapy Device 4245

In a preferred form of the present technology, the therapy device 4245is under the control of the control module 4330 to deliver therapy to apatient 1000.

6.5 Humidifier 5000

6.5.1 Humidifier

Optionally in one form of the present technology there is provided ahumidifier 5000 comprising a water reservoir 5110 and a heating plate5120. The water reservoir is structured to contain a supply of liquid,such as water 5140. The heater plate is arranged to heat at least aportion of the supply of liquid 5140 to produce water vapour for uptakeinto the air flow that passes through the humidifier 5000. Thehumidifier 500 may include a temperature sensor 5130 to monitor thetemperature of the heater plate and optionally additional sensors 5160such as temperature, relative humidity and/or absolute humidity sensors.

A heated air delivery conduit 4172 may optionally be used to reducerainout in the air delivery conduit between the humidifier 5000 and thepatient interface 3000. The heated air delivery conduit 4172 may be asingle limb circuit or a double limb circuit, where one or both of thelimbs may be heated. A heating coil 4174 may be provided within theheated conduit 4174 to heat the air flow as it travels through the airdelivery conduit 4172. The air delivery conduit 4172 may also optionallyinclude one or more sensors 4176, such as temperature, flow, humidity opressure sensors.

The humidifier may be coupled between the device 4000 and the patientinterface 3000 as shown in FIG. 5. Alternatively the humidifier 5000 maybe attached upstream of the device 4000 (not shown). The humidifier 5000may be a separable component to the device 4000 and be coupled via anair delivery conduit 4170 or arranged to directly connect to the device4000. In an alternative arrangement the humidifier 5000 may beintegrally constructed with the device 4000 (not shown). The humidifier5000 is configured to humidify the gas prior to delivery to the patient1000.

The humidifier may use an alternative humidification system such as theCounterStream™ humidification system described in U.S. Pat. No.7,975,687 the contents of which is incorporated herein in its entirety.

6.6 Power Management

6.6.1 Power Usage and Charging Arrangements

As mentioned above the device or ventilator 4000 includes a power sourceconnection that is configured to connect to a range of different powersupply sources: an Alternating Current (AC) power 4434 via an AC powersupply unit (PSU) 4430 using an AC power cord 4432, one or more externalbatteries 4410, 4420, and Direct current (DC) mains power 4460 using aDC power cord 4462. The system may include one or more of thesedifferent power supply sources coupled to the ventilator 4000 at onetime. The power source may be coupled to the device 4000 in series viathe power source connection. The device 4000 may generally only beconnected to the AC PSU 4430 or the DC mains power 4460 at any one time.The ventilator or device 400 may also include an internal battery 4450located within the device as described above that may be used as a powersupply source. In use, generally one of the connected power supplysources may be utilised at a time to provide power to the device 4000.

In some arrangements the internal battery 4450 must be present in thedevice 4000 for ventilation therapy to be provided by the device even ifanother power source is coupled to the ventilator and being used as theprimary source of power. The device 4000 may be able to be turned on buttherapy cannot commence in the absence of the internal battery 4450. Analarm may signal the lack of an internal battery 4450. The requiredpresence of the internal battery 4450 is to ensure therapy can becontinued if the primary or external power supply is interrupted forsome reason, for example during a power cut. The presence of theinternal battery 4450 provides a safety backup for the device 4000.

The controller of the ventilator 4000 may detect the connection of thedifferent power supply sources based on the detection of differentvoltage ranges along the communication signal. The voltage ranges forthe different power supply sources do not overlap. The AC PSU 4430 mayprovide a first voltage range, e.g. 1.3 to 1.8 Volts, the DC mains power4460 may provide a different second voltage range e.g. 0.05 Volts to 1.2Volts, and the external battery may provide a third voltage range, e.g.2.2 to 3 Volts. These voltage ranges are exemplary only and it is to beunderstood that other voltage ranges may be used provided the voltageranges do not overlap.

The device includes a power usage priority scheme to ensure that poweris used from the different power supply sources in a prioritised manner.The AC PSU 4430 has the highest power priority so will always be used atthe primary source of power if attached. Thus, when the AC PSU 4430 iscoupled between a main AC power supply and the device 4000, the AC PSU4430 will have power priority to provide the power supply to the device4000 irrespective of what other forms of power supply sources are alsocoupled to the device 4000. If, as shown in FIG. 4j , one or moreexternal batteries and an internal battery 4450 are also connected inseries then the power provided through the AC PSU 4430 may also be usedto recharge the one or more external batteries 4410, 4420 and/or theinternal battery 4450 as required whilst also providing the power forrunning the ventilator 4000. However at all times the running of theventilator 4000 takes priority over the use of the power supplied andthe recharging of any batteries is reduced when more power is requiredby the ventilator 4000. In some arrangements the AC PSU 4430 may providepower to recharge the batteries when the output power required by theventilator is below a threshold. The threshold may be the maximum poweror close to the maximum power that the AC PSU 4430 can supply, forexample 90 Watts. Thus, a dynamic power management system is used tocontrol the recharging of the batteries.

There may be a priority for the recharging scheme, such that when the ACmains power is used for recharging, the internal battery 4450 has thehighest priority and is preferably recharged first. The one or moreexternal batteries may be recharged when the internal battery 4450 issubstantially fully recharged. The recharge of the one or more externalbatteries also may occur in series with the most downstream externalbattery 4410, i.e. the external battery closest to the ventilator 4000,being recharged before the next external battery in the series. In suchan arrangement each external battery is recharged along the series withthe last or most upstream external battery 4420 being the last to berecharged.

FIG. 4k shows an arrangement where the AC PSU 4430 is not coupled to adevice or ventilator 4000 but is used to recharge the external batteries4410, 4420. In this arrangement the AC PSU 4430 is connected to a mainsAC power supply 4434 to provide power to charge one or more externalbatteries, shown as charging two external batteries, an upstreamexternal battery 4420 and a downstream external battery 4410. However,further external batteries may be connection in series between theupstream external battery 4420 and the downstream external battery 4410.In this configuration the downstream external battery 4410 is notconnected to a device or ventilator 4000. In some arrangements accordingto the technology the external batteries are recharged in a seriesfashion along the series, for example the furthest downstream externalbattery 4410, i.e. the external battery that would be closest to thedevice 4000 when connected or furthest from the AC PSU 4430, may berecharged first and then the next external battery in the series may berecharged. The recharging scheme continues along the series until allthe external batteries connected in the series are recharged, the lastor most upstream external battery 4420 being the last to be recharged.It is to be understood that recharging may occur in a different orderfor example with the upstream external battery 4420 being rechargedfirst and the downstream external battery 4410 being recharged last. Inanother arrangement all the external batteries may be rechargedsimultaneously.

If DC mains power 4460 is coupled to the ventilator 4000, irrespectiveof whether the internal battery is present or one or more externalbatteries are connected in series, see FIG. 4m , the DC mains power 4460will have the power priority to provide the power supply to the device4000. In such an arrangement the internal battery 4450, may also becharged by the DC mains power 4460 if sufficient power is available forrecharging and running the device 4000. The power requirements for therunning of the device 4000 take priority over the recharging of theinternal battery 4450. In some arrangements the one or more externalbatteries 4410, 4420, if present, may not be recharged by the DC mainspower 4460 irrespective of the level of DC power available. In otherarrangements, if sufficient DC power is available, the externalbatteries 4410, 4420 may be recharged by the DC power. It is to beunderstood that the one or more external batteries 4410, 4420 are notrequired to be connected to the ventilator when the ventilator isconnected to the DC mains power 4460. Preferably the internal battery4450 is present within the ventilator 4000 when the ventilator is beingpowered by the DC mains power 4460 to provide a power backup asdiscussed above.

FIG. 4l illustrates an arrangement where one or more external batteriesare used to run the ventilator or device 4000. The external batteriesmay be connected to the ventilator using an electrical cable, such as aDC power cord 4462, and each external battery is connected to theadjacent external battery using an electrical cable such as a DC powercord. Each external battery may include an input port and output portstructured to receive the electrical cable between adjacent externalbatteries. The external battery closest to the device 4000 (e.g. adownstream external battery 4410), is connected to the power sourceconnection of the device 4000 via an electrical cable, e.g. a DC powercord 4462. If more than one external battery is connected in series tothe ventilator 4000 then an external battery power usage priority isused to determine from which external battery power will be supplied.The external battery being used to supply the power source to theventilator in use may be considered the power supplying externalbattery.

In one arrangement the power from the external battery located furthestfrom the ventilator 4000 in the series, e.g. the upstream externalbattery 4420 as shown in FIG. 4l , will be used first to run theventilator 4000, and will be the initial power supply external battery.Once the power has been substantially exhausted from the upstreamexternal battery 4420 then the power will be used from the next externalbattery in the series and this external battery will become the powersupplying external battery, e.g. the downstream external battery 4410 inFIG. 4l , to run the ventilator 4000. If more than two externalbatteries are connected in series to the ventilator 4000 then the powerfrom each external battery will be used in series from the furthest ormost upstream external battery along the series to the closest or mostdownstream external battery in the series. When all the power from allthe external batteries has been substantially exhausted then the powerin the internal battery 4450 will be used to run the ventilator 4000. Insuch an arrangement the power in the internal battery 4450 is the lastto be used to allow a power safety backup should any power problemsoccur particularly when connected to AC mains power 4434 or DC mainspower 4460.

In an alternative arrangement the external battery power usage prioritymay use the power from the external battery located closest to theventilator 4000, i.e. the downstream external battery 4410, first andthen use the power in the adjacent external battery in the series nextand then continue along the series so that the external battery furthestfrom the ventilator 4000, i.e. the upstream battery 4420, is used last.

In a preferred aspect of the technology, the power usage and rechargingare configured so that the internal battery 4450 is the last to be usedand the first to be recharged.

6.6.2 Communication

In an aspect of the present technology the device or ventilator 4000 isconfigured to provide an estimate of the total remaining capacity orstate of charge available from all coupled battery power sources, i.e.the internal battery 4450 and/or one or more external batteries 4410,4420. The device 4000 may provide an estimate of a total capacityavailable as an estimate of the total run time remaining based on thepresent rate of power usage by the ventilator.

Each external battery has an input port and output port to relaycommunication signals or information along the chain to and from thecontroller of the ventilator 4000. Communication signals are relayedalong the series from upstream external batteries 4410 to downstreamexternal batteries 4410 back to the ventilator 4000 and in the reversedirection from the ventilator 4000 along the series to the most upstreamexternal battery 4420. If the internal battery 4450 is present then thecommunication signals may also be provided through the internal battery4450 or alternatively the internal battery 4450 may communicateindependently with the ventilator controller.

The battery that is presently in use, i.e. being used to run the device,is configured to determine the remaining run time (hours) available foruse as a function of the batteries present level of charge (milliAmperes(mA)) and the present rate of usage (mA/hr) being used by theventilator. The other batteries, such as other external batteries and/orthe internal battery, may each also determine their own remainingcapacity and send this information to the battery that is currentlypowering the system. It is the battery that is currently powering thesystem that determines the current rate of power usage. It is to beunderstood that the time and rates may be provided in different units oftime such as minutes or seconds instead of hours or as a combination ofhours, minutes and/or seconds.

For example when the system is running from the most upstream externalbattery 4420 as shown in FIG. 4l , the controller 4230 of the ventilator4000 may send a request for the remaining run time to the mostupstream-battery 4420. The controller 4230 may send a request forbattery capacity information to the internal battery 4450 as the mostdownstream battery coupled to the ventilator. The internal battery 4450may then send a request to the downstream external battery 4410, i.e.the external battery connected closest to the ventilator 4000. Thedownstream external battery 4410 may then send a request for batterycapacity information to the adjacent external battery and this continuesalong the series of external batteries to the most upstream externalbattery 4420 that is providing power or capable of providing power. Theupstream external battery 4420 provides the remaining capacity (RC)information and the remaining run time (RRT) information based on thecurrent rate of power usage by the ventilator from this upstreamexternal battery 4420. The remaining capacity (RC) information and theremaining run time (RRT) information is passed back along the series tothe downstream external battery 4410. The downstream external battery4410 would also request the remaining capacity (RC) information from anyother external batteries connected in the series between the upstreamexternal battery 4410 and the downstream external battery 4410 ifpresent, (not shown in FIG. 4l ) to provide a total external batteriesremaining capacity. In one arrangement the most downstream externalbattery 4410 may then send the information to the internal battery 4450,which also provides information regarding its own remaining capacity.The internal battery 4450 may determine an estimate of the totalremaining run time (TRRT) or send the information to the controller 4230to determine an estimate of the total remaining run time (TRRT). In thisarrangement the internal battery 4450 or controller 4230 will estimatethe total remaining run time (TRRT) using the following:

$\begin{matrix}{{TRRT} = {\frac{\left( {{{Bat}(n)}{\_ RC}} \right) + \left( {{{Bat}\left( {n - 1} \right)}{\_ RC}} \right) + \ldots + \left( {{{Bat}(1)}{\_ RC}} \right)}{{{Bat}(n)}{\_ RC}} \times {BatnRRT}}} & \lbrack 1\rbrack\end{matrix}$

Wherein there are n number of batteries in the series and battery n isthe most upstream battery (e.g the upstream external battery 4420 inFIGS. 4j to 4m ) that is capable of providing power to run theventilator 4000, such as when power is being provided by AC mains or DCmains, or is the battery being used to provide the power to run theventilator 4000, TRRT is the total remaining run time for all of the nbatteries in the series, Bat(n)_RC is the remaining capacity of the mostupstream battery that has power available (e.g. the upstream externalbattery 4450 in FIG. 4m ), Bat(n−1)_RC is the remaining capacity of thebattery adjacent the most upstream battery (e.g. the downstream externalbattery 4410 in FIG. 4m ), Bat(1)_RC is the remaining capacity of themost downstream battery (e.g. the internal battery 4450 in FIG. 4m ) andBatnRRT is the Remaining Run Time of Battery n in hours (and/or minutesand/or seconds). It is to be understood that if there are batteriesbetween the most downstream external battery n and the most upstreamexternal battery then the calculation will also include the remainingcapacity of each of the additional external batteries.

The remaining capacity in the above calculation [1] is preferably theactual battery remaining capacity in mA/hrs or some other absolute unitsrather than a percentage state of charge. This is due to the percentagestate of charge may vary between batteries and over the life of thebatteries such that errors may be introduced if percentage state ofcharge (SOC) is used. For example 100% SOC in one battery may be adifferent actual amount of mAhrs as the % SOC is relative to the maximumcurrent available capacity in the pack which reduces with charge anddischarge cycles, e.g. after 400 cycles the full capacity may only be80% of the new pack capacity.

In an alternative arrangement the internal battery 4450 and the externalbatteries 4410, 4420 do not directly communicate with each other. Thecontroller of the ventilator sends a signal to the downstream externalbattery 4410 to request the external battery remaining capacity and/orremaining run time for the series of external batteries. A determinationof the total remaining run time of the external batteries is determinedindependently of a calculation of the total remaining run time of theinternal battery 4450. In this arrangement the downstream externalbattery 4410 may perform the above calculation [1] to determine thetotal external battery remaining run time of all the external batteriesbased on the remaining capacity information received from all of theupstream external batteries in the series. Alternatively the upstreamexternal battery 4420 may perform the calculation of total externalbattery remaining run time [1] based on received capacity informationfrom all of the downstream external batteries in the series.

If the upstream external battery n has substantially discharged so thatthe power is being supplied from the next external battery downstream inthe series, n−1, there will be no signal regarding charge from theupstream external battery n sent to the downstream external battery4410. In this case the next external battery in the series n−1, becomesthe n battery so only the charge remaining from the external batterypresently providing the power or capable of providing power, n, and theother external batteries downstream from this external battery will beused in the calculation of the total remaining run time.

The controller of the ventilator may send an independent request signalto the internal battery 4450 for the internal battery remaining capacityand/or remaining run time. The internal battery 4450 may be configuredto determine the remaining capacity of the internal battery 4450 andsend this information to the controller.

In some arrangements the controller of the ventilator 4000 may beconfigured to receive the determined Total remaining run timeinformation from all the battery sources, i.e. the internal battery andall the external batteries, as described above.

In other arrangements the controller may to be configured to receive theremaining capacity information from the internal battery 4450 and theseries of external batteries 4410, 4420 and perform the calculation [1]above to determine the total battery remaining run time. The ventilatorcontroller 4230 may be configured to display the total remaining runtime estimate of all the battery sources on the user interface ordisplay 4294 of the ventilator in hours and/or minutes and/or seconds.The ventilator 4000 may be configured to display the total remaining runtime of each individual battery source or all external batteries and theinternal battery in hours and/or minutes and/or seconds on the display4292.

In a further aspect of the technology the controller of the ventilatormay request an estimate of the total remaining capacity from coupledbatteries, either from the external batteries and internal batteriestogether or from the external batteries and the internal batteryindependently. The ventilator may show the remaining capacity of thetotal battery sources, external batteries and/or internal batteries, inmilliampere per hour (mA/hr) and/or as a percentage of remaining powerbased on the total level of power that the battery sources are capableof providing.

In one form of an aspect of the present technology the voltage supply issplit to provide a first voltage rail and a second voltage rail from themain voltage rail, for example a 30V rail. The first voltage rail may beconfigured to supply power for the core ventilation system, i.e. to runthe essential logic required to run the device 4000. The second voltagerail may be configured to supply power for the peripheral circuits. Theperipheral circuits may include power to run the user interface such asthe LCD or touch screen, data input/output devices such as USB orEthernet or remote interfaces. In this arrangement failures or shutdowns of the peripheral circuits are less likely to affect the coreventilation system, thus allowing the core ventilation to continue torun. In one example the first voltage rail and the second voltage railmay be 5V rails. Alternatively the first voltage rail and the secondvoltage rails may provide different voltage supply levels.

6.6.3 Power Efficiency

In a further aspect of the present technology the device or ventilator4000 may include an energy regeneration system coupled to the mainblower 4104. In this arrangement, see FIG. 4n , when the main blower isdecelerated, such as when cycling from an inspiration set pressure to anexpiration set pressure, the energy stored within the inertia of theblower may be stored in an energy storage unit 4510. The energy storageunit 4510 may include at least one capacitor, a group of capacitors orsuper capacitors or a battery. The energy storage unit 4510 ispositioned in parallel with the input power supply 4210. The energy isregenerated or stored in the energy storage unit 4510 for use to run thedevice or components of the device 4000 for short periods of time ineach breathing cycle until the energy in the energy storage unit hasdecayed to a set point. For example the short period of time may beapproximately 200 to 500 milliseconds (ms), such as 300 ms. However, theduration depends on the energy recovered from the main blower inertiaand the system operation current, i.e. the settings of the device at thetime of energy regeneration. An optional diode 4520 as indicated by thedashed lines may be located between the energy storage unit 4510 and theinput power supply 4210 depending upon whether the input power supply4210 may tolerate excursions in the voltage from the energy storage unit4510. In this arrangement the energy storage unit 4510 is only used toprovide power to the main blower and the control system 4230 is poweredfrom the power input supply.

In one aspect of the present technology when the energy storage unit4510 is providing the power for running the ventilator 4000, a regulatorswitch switches off the power from the input power supply 4210.Switching off the input power supply when the device is being run fromthe energy storage unit increases the power efficiency of the system.

As shown in FIG. 4o , a voltage boost regulator 4530 is powered from theinput power supply, which may include an external input supply 4540and/or an internal battery 4450. Switches control whether the power issupplied from the external input supply 4540 or the internal battery4450. The external input supply 4540 may include any one of the AC mainspower 4434, DC Main power 4460 or an external battery 4420, 4410. Thecontrol of this switchover is performed by a battery charger internalcircuit, when the external input supply drops below a firstpredetermined voltage such as approximately 10.5V, the system switchesto the internal battery 4450, when the external input supply 4540recovers and the voltage reaches above the first predetermined voltageor reaches a second predetermined voltage, such as approximately 11V,the system switches back to the external supply input 4540.

During motor deceleration, a motor driver 4105 continues to drive themain blower 4104 using a software control to maintain commutation of themotor but at a low drive level e.g. 10% drive. As the main blower 4104decelerates then energy that is stored in the angular momentum andinertia of the main blower is transferred to a small amount of heat inthe blower and motor control FETs and stored in the energy storage unit4510, for example in 2×2700 uF motor capacitors. Consequently, the motorcapacitor voltage increases from a first predetermined voltage limit,for example 30V, up to a maximum voltage, for example 45V. When thevoltage boost regulator output exceeds a second predetermined voltagelimit, for example 31V, the voltage boost regulator 4530 over voltageprotection circuitry activates which turns off the voltage boostregulator 4530 which turns off the input power supply 4540, 4450. Thesystem then runs from the energy stored on the energy storage unit 4510,for example the motor capacitors, until the voltage drops below thefirst predetermined voltage limit and the voltage boost regulator 4530is restarted.

Advantageously, the energy recovered from the blower inertia is notinstantly converted to heat so less heat dissipation is required. Inaddition, the energy recovered means the losses in the voltage boostregulator are turned off for the duration of time that the system isrunning from the energy storage unit. Hence reducing heat generationfrom the voltage boost regulator during high drive cases. Thus inaspects of the present technology the heat generated during decelerationof the main blower may be decreased due to the energy being stored inthe energy storage unit 4510.

The increased power efficiency gained from recovering the main blowerenergy during deceleration and turning off the power input supply 4210increases the efficiency of the internal battery 4450 and externalbatteries 4410, 4420, if present and being used as the present powersource.

6.7 Alarm Systems

The device or ventilator 4000 may comprise an alarm system that providesvisual and/or audible signals to provide an alert of some condition thatrequires attention. The ventilator 4000 may include output devices 4290in the form of one or more audible alarms such as buzzers 4296 and/orone or more visual alarms, such as LEDs 4298 to provide an alertindication for an alarm condition. If multiple buzzers 4296 are presentthen each buzzer 4296 may produce a different alert sound or differentvolumes of sound and be used to indicate different types of alarmconditions. If multiple LED's 4298 are present each LED 4298 may have adifferent colour or level of brightness to indicate different types ofalarm conditions.

The alarm conditions may include a range of different conditions thateffect the device or therapy and may include a power supply issue (forexample no internal battery attached, loss of external power supply, lowbattery, battery fault etc.), pressure supply issue (for example highpressure, high expiratory pressure, low PEEP, high PEEP, low peakinspiratory pressure, etc.), ventilation parameter issue (for examplelow or high tidal volume on inspiration or expiration, low or highminute ventilation on inspiration or expiration, low or high respiratoryrate, occurrence of an apnea, etc.), Oximetry issues (for example low orhigh SpO₂ level, low or high pulse rate etc.), oxygen supply issues(only provided when an oxygen sensor is connected and may monitor low orhigh FiO₂), breathing circuit issues (for example high leak, incorrectcircuit, pressure line disconnected, etc.) and system faults includingfaults with a blower, a sensor, battery communication, software,operating conditions etc.

The visual alarm may include the lighting or flashing of an alarm bar4026 on the ventilator 4000 and or the sounding of an audible alarm inthe ventilator 4000. An alarm message may be displayed on the userinterface. There may be a priority of alarms, such as high, medium andlow alarm and the alarm alert may vary for the different priorityalarms. For example the high priority alarm may provide a red flashinglight on the alarm bar 4026 and a first predetermined number of beeps ofan audible alarm at a first predetermined frequency. A medium priorityalarm may provide a yellow flashing light on the alarm bar 4026 and asecond predetermined number of beeps of an audible alarm at a secondpredetermined frequency. A low priority alarm may provide a non-flashinglight on the alarm bar 4026 and a third predetermined number of beeps ofan audible alarm at a third predetermined frequency. The firstpredetermined number of beeps may be higher than the secondpredetermined number of beeps and the second predetermined number ofbeeps may be higher than the third predetermined number of beeps. Alsothe first predetermined frequency may be shorter than the secondpredetermined frequency and the second predetermined frequency may beshorter than the third predetermined frequency. However, it is to beunderstood other alarm priority arrangements may be used.

The volume of the audible alarms may be adjusted using the controlsettings available via the user interface on the device. The audiblealarm may be temporarily muted for a predetermined time, such as 1, 2,3, 4 or 5 minutes, by pressing a mute button on the user interface. Ifthe alarm condition is still present after the muted predetermined timehas passed then the audible alarm will sound again.

Some types of alarms, such as low priority and non-life threateningcondition alarms may be manually reset by a user causing the visualand/or audible alarm to be turned off. Whilst other alarms may not bereset unless the alarm condition is corrected. Such critical alarms maybe automatically reset by the ventilator upon correction of the alarmcondition or reset enabled only after correction of the condition thatcaused the alarm.

In one aspect the system may be configured to attach a remote alarm 4660to allow alarms to be placed at an alternative location to theventilator 4000, for example in another room. The remote alarm 4660 isconfigured to alert carers of an alarm event. The remote alarm may bebattery powered and connected to the device 4000 via a cable. Optionallya second remote alarm may be connected to the first remote alarm toenable placement of remote alarms in two separate locations.

In one aspect the system may be configured to attach a remote control4650 that enables a user to operate an alarm as a nurse or carer alarmby pressing a button located on the remote control 4650. The remotecontrol may be coupled to the device 4000 via a cable.

In one aspect of the present technology the alarm system includes aHardware Alarm Controller (HAC) 4610. The HAC 4610 drives the alarmbuzzers 4292 and/or LEDs 4294 to deliver the predetermined alarmpatterns for the different alarm priorities as described above. FIG. 4pshows a schematic of the HAC control system. The HAC monitors the mainboard processor 4620 and the pneumatic block processor 4630. Althoughthe main board processor and pneumatic block processor 4630 are shown astwo different blocks in FIG. 4p it is to be understood that these may bepresent on a single PCB or on separate PCBs. The pneumatic blockprocessor 4630 and the main board processor 4620 can communicate witheach other to enable correct running of the device and therapies.

The Pneumatic block processor 4630 may also comprises a pneumatic blocksafety circuit 4632 that monitors the occurrence of hardware errors inthe ventilator delivery system, such as pressure, current or temperatureerrors and software errors.

An alarm watchdog system monitors the main board processor 4620 and thepneumatic block processor 4630 and sends regular signals (2), (5), 4622,4634 to the HAC to inform the HAC that the main board processor 4620 andthe pneumatic block processor 4630 are functioning correctly. Thepneumatic block safety circuit 4632 may generate the pneumatic blockwatchdog signal 4634. If the HAC 4610 does not receive either of thewatchdog signals 4622, 4634 on time then the HAC raises an alarm andsends a safety assert state signal (6) to the pneumatic block processor4630. The safety assert state signal (6) causes the system to be placedin a safe state. A safe state may include turning off the main blower4104 and the PEEP Blower 4124, turning off the oxygen valve drive 4640if present, deactivating the PEEP electrovalve 4136 and activating(energizing) the non-return valve 4114 and the safety valve 4085 (seeFIG. 40.

The HAC 4610 may also monitor the power supply for the ventilator 4000,via a signal 4670, for example a VCORE_Good signal, and will raise analarm if power fails during operation of the ventilator 4000.

The HAC may be coupled to a HAC super capacitor (not shown) that ispowered from a charger that runs from the first voltage rail asdescribed above that is configured to run the core ventilation systems.Thus, the HAC and HAC super capacitor are considered part of the coreventilation system, i.e. are essential logic required to run the device4000. The HAC super capacitor may be continually held fully chargedwhile the system is being powered. The HAC super capacitor is configuredto supply power to one or more of alarms 4290 if a power failure occursto raise a total power failure alarm. Preferably the total power failurealarm is an audible alarm, and the HAC super capacitor is configured topower one or more of the buzzers 4292. Optionally the visual alarms maynot be activated by the HAC super capacitor power to extend the run timeon total power fail for the audible alarm.

The HAC 4610 has bi-directional communication with the main boardprocessor 4620 as the main board processor 4620 software may beresponsible for activating and deactivating the alarms based onpredefined alarm algorithms that are designed for each type of alarmcondition. The main board processor 4620 may then signal the HAC 4610 toactivate the buzzers 4292 and/or LEDs 4294. Each alarm algorithmcomprises inputs settings such as thresholds or parameter to be met toactivate an alarm condition. Alarm activation parameters may be derivedfrom the pneumatic block processor 4630 or the main board processor4620. In certain arrangements the ventilator 4000 may include an Audiopause button 4610 that may allow some alarms to be muted by pressing theAudio pause button 4610 depending on the type and priority level of thealarm. When the Audio pause button 4610 is pressed a signal is sent tothe HAC 4610 to turn off the output devices 4290, i.e. buzzers 4292and/or LEDs 4294. A signal is also sent to the main board processor 4620to advise of the paused alarm and start a timer for the paused alarm.The alarm will be restarted after a predetermined time has passed andthe alarm condition has not been overcome. An audio pause LED may bepresent and be activated when an alarm is paused.

The remote alarm 4650 communicates with the main board processor 4620 tosignal the activation of an alarm, i.e. a carer alarm. The main boardprocessor 4620 may then signal the HAC 4610 to activate the buzzers 4292and/or LEDs 4294 as required to raise the alarm alert.

The remote alarm 4610 is connected to the HAC 4610 so that any alarmsraised by the HAC 4660 are sent to the remote alarm 4660.

6.8 Glossary

For the purposes of the present technology disclosure, in certain formsof the present technology, one or more of the following definitions mayapply. In other forms of the present technology, alternative definitionsmay apply.

6.8.1 General

Air: In certain forms of the present technology, air supplied to apatient may be atmospheric air, and in other forms of the presenttechnology atmospheric air may be supplemented with oxygen.

Continuous Positive Airway Pressure (CPAP): CPAP treatment will be takento mean the application of a supply of air or breathable gas to theentrance to the airways at a pressure that is continuously positive withrespect to atmosphere, and preferably approximately constant through arespiratory cycle of a patient. In some forms, the pressure at theentrance to the airways will vary by a few centimeters of water within asingle respiratory cycle, for example being higher during inhalation andlower during exhalation. In some forms, the pressure at the entrance tothe airways will be slightly higher during exhalation, and slightlylower during inhalation. In some forms, the pressure will vary betweendifferent respiratory cycles of the patient, for example being increasedin response to detection of indications of partial upper airwayobstruction, and decreased in the absence of indications of partialupper airway obstruction.

6.8.2 Aspects of Devices

Air circuit: A conduit or tube constructed and arranged in use todeliver a supply of air or breathable gas between a device and a patientinterface. In particular, the air circuit may be in fluid connectionwith the outlet of the pneumatic block and the patient interface. Theair circuit may be referred to as air delivery tube. In some cases theremay be separate limbs of the circuit for inhalation and exhalation. Inother cases a single limb is used.

Blower or flow generator: A device that delivers a flow of air at apressure above ambient pressure.

Controller: A device, or portion of a device that adjusts an outputbased on an input. For example one form of controller has a variablethat is under control—the control variable—that constitutes the input tothe device. The output of the device is a function of the current valueof the control variable, and a set point for the variable. Aservo-ventilator may include a controller that has ventilation as aninput, a target ventilation as the set point, and level of pressuresupport as an output. Other forms of input may be one or more of oxygensaturation (SaO₂), partial pressure of carbon dioxide (PCO₂), movement,a signal from a photoplethysmogram, and peak flow. The set point of thecontroller may be one or more of fixed, variable or learned. Forexample, the set point in a ventilator may be a long term average of themeasured ventilation of a patient. Another ventilator may have aventilation set point that changes with time. A pressure controller maybe configured to control a blower or pump to deliver air at a particularpressure.

Therapy: Therapy in the present context may be one or more of positivepressure therapy, oxygen therapy, carbon dioxide therapy, control ofdead space, and the administration of a drug.

Motor: A device for converting electrical energy into rotary movement ofa member. In the present context the rotating member is an impeller,which rotates in place around a fixed axis so as to impart a pressureincrease to air moving along the axis of rotation.

Positive Airway Pressure (PAP) device: A device for providing a supplyof air at positive pressure to the airways.

Transducers: A device for converting one form of energy or signal intoanother. A transducer may be a sensor or detector for convertingmechanical energy (such as movement) into an electrical signal. Examplesof transducers include pressure sensors, flow sensors, carbon dioxide(CO₂) sensors, oxygen (O₂) sensors, effort sensors, movement sensors,noise sensors, a plethysmograph, and cameras.

Volute: The casing of the centrifugal pump that receives the air beingpumped by the impeller, slowing down the velocity of flow of air andincreasing the pressure. The cross-section of the volute increases inarea towards the discharge port.

6.8.3 Aspects of the Respiratory Cycle

Apnea: Preferably, apnea will be said to have occurred when flow fallsbelow a predetermined threshold for a duration, e.g. 10 seconds. Anobstructive apnea will be said to have occurred when, despite patienteffort, some obstruction of the airway does not allow air to flow. Acentral apnea will be said to have occurred when an apnea is detectedthat is due to a reduction in breathing effort, or the absence ofbreathing effort.

Breathing rate: The rate of spontaneous respiration of a patient,usually measured in breaths per minute.

Duty cycle: The ratio of inhalation time, Ti to total breath time, Ttot.

Effort (breathing): Preferably breathing effort will be said to be thework done by a spontaneously breathing person attempting to breathe.

Expiratory portion of a breathing cycle: The period from the start ofexpiratory flow to the start of inspiratory flow.

Flow limitation: Preferably, flow limitation will be taken to be thestate of affairs in a patient's respiration where an increase in effortby the patient does not give rise to a corresponding increase in flow.Where flow limitation occurs during an inspiratory portion of thebreathing cycle it may be described as inspiratory flow limitation.Where flow limitation occurs during an expiratory portion of thebreathing cycle it may be described as expiratory flow limitation.

Types of flow limited inspiratory waveforms:

(i) Flattened: Having a rise followed by a relatively flat portion,followed by a fall.

(ii) M-shaped: Having two local peaks, one at the leading edge, and oneat the trailing edge, and a relatively flat portion between the twopeaks.

(iii) Chair-shaped: Having a single local peak, the peak being at theleading edge, followed by a relatively flat portion.

(iv) Reverse-chair shaped: Having a relatively flat portion followed bysingle local peak, the peak being at the trailing edge.

Hypopnea: Preferably, a hypopnea will be taken to be a reduction inflow, but not a cessation of flow. In one form, a hypopnea may be saidto have occurred when there is a reduction in flow below a threshold fora duration. In one form in adults, the following either of the followingmay be regarded as being hypopneas:

-   -   (i) a 30% reduction in patient breathing for at least 10 seconds        plus an associated 4% desaturation; or    -   (ii) a reduction in patient breathing (but less than 50%) for at        least 10 seconds, with an associated desaturation of at least 3%        or an arousal.

Inspiratory portion of a breathing cycle: Preferably the period from thestart of inspiratory flow to the start of expiratory flow will be takento be the inspiratory portion of a breathing cycle.

Patency (airway): The degree of the airway being open, or the extent towhich the airway is open. A patent airway is open. Airway patency may bequantified, for example with a value of one (1) being patent, and avalue of zero (0), being closed.

Positive End-Expiratory Pressure (PEEP): The pressure above atmospherein the lungs that exists at the end of expiration.

Peak flow (Qpeak): The maximum value of flow during the inspiratoryportion of the respiratory flow waveform.

Respiratory flow, airflow, patient airflow, respiratory airflow (Qr):These synonymous terms may be understood to refer to the device'sestimate of respiratory airflow, as opposed to “true respiratory flow”or “true respiratory airflow”, which is the actual respiratory flowexperienced by the patient, usually expressed in litres per minute.

Tidal volume (Vt): The volume of air inhaled or exhaled during normalbreathing, when extra effort is not applied.

(inhalation) Time (Ti): The duration of the inspiratory portion of therespiratory flow waveform.

(exhalation) Time (Te): The duration of the expiratory portion of therespiratory flow waveform.

(total) Time (Ttot): The total duration between the start of theinspiratory portion of one respiratory flow waveform and the start ofthe inspiratory portion of the following respiratory flow waveform.

Typical recent ventilation: The value of ventilation around which recentvalues over some predetermined timescale tend to cluster, that is, ameasure of the central tendency of the recent values of ventilation.

Upper airway obstruction (UAO): includes both partial and total upperairway obstruction. This may be associated with a state of flowlimitation, in which the level of flow increases only slightly or mayeven decrease as the pressure difference across the upper airwayincreases (Starling resistor behaviour).

Ventilation (Vent): A measure of the total amount of gas being exchangedby the patient's respiratory system, including both inspiratory andexpiratory flow, per unit time. When expressed as a volume per minute,this quantity is often referred to as “minute ventilation”. Minuteventilation is sometimes given simply as a volume, understood to be thevolume per minute.

6.8.4 Device Parameters

Flow rate: The instantaneous volume (or mass) of air delivered per unittime. While flow rate and ventilation have the same dimensions of volumeor mass per unit time, flow rate is measured over a much shorter periodof time. Flow may be nominally positive for the inspiratory portion of abreathing cycle of a patient, and hence negative for the expiratoryportion of the breathing cycle of a patient. In some cases, a referenceto flow rate will be a reference to a scalar quantity, namely a quantityhaving magnitude only. In other cases, a reference to flow rate will bea reference to a vector quantity, namely a quantity having bothmagnitude and direction. Flow will be given the symbol Q. Total flow,Qt, is the flow of air leaving the device. Vent flow, Qv, is the flow ofair leaving a vent to allow washout of exhaled gases. Leak flow, Ql, isthe flow rate of unintentional leak from a patient interface system.Respiratory flow, Qr, is the flow of air that is received into thepatient's respiratory system.

Leak: Preferably, the word leak will be taken to be a flow of air to theambient. Leak may be intentional, for example to allow for the washoutof exhaled CO₂. Leak may be unintentional, for example, as the result ofan incomplete seal between a mask and a patient's face.

Pressure: Force per unit area. Pressure may be measured in a range ofunits, including cmH₂O, g-f/cm², hectopascal. 1cmH₂O is equal to 1g-f/cm² and is approximately 0.98 hectopascal. In this specification,unless otherwise stated, pressure is given in units of cmH₂O. For nasalCPAP treatment of OSA, a reference to treatment pressure is a referenceto a pressure in the range of about 4-20 cmH₂O, or about 4-30 cmH₂O. Thepressure in the patient interface is given the symbol Pm.

Sound Power: The energy per unit time carried by a sound wave. The soundpower is proportional to the square of sound pressure multiplied by thearea of the wavefront. Sound power is usually given in decibels SWL,that is, decibels relative to a reference power, normally taken as 10⁻¹²watt.

Sound Pressure: The local deviation from ambient pressure at a giventime instant as a result of a sound wave travelling through a medium.Sound power is usually given in decibels SPL, that is, decibels relativeto a reference power, normally taken as 20×10⁻⁶ pascal (Pa), consideredthe threshold of human hearing.

6.8.5 Terms for Ventilators

Adaptive Servo-Ventilator: A ventilator that has a changeable, ratherthan fixed target ventilation. The changeable target ventilation may belearned from some characteristic of the patient, for example, arespiratory characteristic of the patient.

Backup rate: A parameter of a ventilator that establishes the minimumrespiration rate (typically in number of breaths per minute) that theventilator will deliver to the patient, if not otherwise triggered.

Cycled: The termination of a ventilator's inspiratory phase and may alsobe known as Expiratory Trigger to indicate the start of expiration. Whena ventilator delivers a breath to a spontaneously breathing patient, atthe end of the inspiratory portion of the breathing cycle, theventilator is said to be cycled to stop delivering the breath.

EPAP (or EEP): Expiratory Positive Airway Pressure (EPAP) is thepressure to be delivered to the patient during expiration or a basepressure, to which a pressure varying within the breath is added toproduce the desired mask pressure which the ventilator will attempt toachieve during expiration.

IPAP: desired mask pressure which the ventilator will attempt to achieveduring the inspiratory portion of the breath.

Pressure support: A number that is indicative of the increase inpressure during ventilator inspiration over that during ventilatorexpiration, and generally means the difference in pressure between themaximum value during inspiration and the minimum value during expiration(e.g., PS=IPAP−EPAP). In some contexts pressure support means thedifference which the ventilator aims to achieve, rather than what itactually achieves.

Servo-ventilator: A ventilator that measures patient ventilation has atarget ventilation, and which adjusts the level of pressure support tobring the patient ventilation towards the target ventilation.

Spontaneous/Timed (S/T)—A mode of a ventilator or other device thatattempts to detect the initiation of a breath of a spontaneouslybreathing patient. If however, the device is unable to detect a breathwithin a predetermined period of time, the device will automaticallyinitiate delivery of the breath.

Swing: Equivalent term to pressure support.

Triggered: When a ventilator delivers a breath of air to a spontaneouslybreathing patient, it is said to be triggered to do so at the initiationof the inspiratory portion of the breathing cycle by the patient'sefforts.

Ventilator: A mechanical device that provides pressure support to apatient to perform some or all of the work of breathing.

6.8.6 Anatomy of the Respiratory System

Diaphragm: A sheet of muscle that extends across the bottom of the ribcage. The diaphragm separates the thoracic cavity, containing the heart,lungs and ribs, from the abdominal cavity. As the diaphragm contractsthe volume of the thoracic cavity increases and air is drawn into thelungs.

Larynx: The larynx, or voice box houses the vocal folds and connects theinferior part of the pharynx (hypopharynx) with the trachea.

Lungs: The organs of respiration in humans. The conducting zone of thelungs contains the trachea, the bronchi, the bronchioles, and theterminal bronchioles. The respiratory zone contains the respiratorybronchioles, the alveolar ducts, and the alveoli.

Nasal cavity: The nasal cavity (or nasal fossa) is a large air filledspace above and behind the nose in the middle of the face. The nasalcavity is divided in two by a vertical fin called the nasal septum. Onthe sides of the nasal cavity are three horizontal outgrowths callednasal conchae (singular “concha”) or turbinates. To the front of thenasal cavity is the nose, while the back blends, via the choanae, intothe nasopharynx.

Pharynx: The part of the throat situated immediately inferior to (below)the nasal cavity, and superior to the oesophagus and larynx. The pharynxis conventionally divided into three sections: the nasopharynx(epipharynx) (the nasal part of the pharynx), the oropharynx(mesopharynx) (the oral part of the pharynx), and the laryngopharynx(hypopharynx).

6.8.7 Aspects of a Patient Interface

Anti-asphyxia valve (AAV): The component or sub-assembly of a masksystem that, by opening to atmosphere in a failsafe manner, reduces therisk of excessive CO₂ rebreathing by a patient.

Headgear: Headgear will be taken to mean a form of positioning andstabilizing structure designed for use on a head. Preferably theheadgear comprises a collection of one or more struts, ties andstiffeners configured to locate and retain a patient interface inposition on a patient's face for delivery of respiratory therapy. Someties are formed of a soft, flexible, elastic material such as alaminated composite of foam and fabric.

Plenum chamber: a mask plenum chamber will be taken to a mean portion ofa patient interface having walls enclosing a volume of space, the volumehaving air therein pressurised above atmospheric pressure in use. Ashell may form part of the walls of a mask plenum chamber. In one form,a region of the patient's face forms one of the walls of the plenumchamber.

Seal: The noun form (“a seal”) will be taken to mean a structure orbarrier that intentionally resists the flow of air through the interfaceof two surfaces. The verb form (“to seal”) will be taken to mean toresist a flow of air.

Swivel: (noun) A subassembly of components configured to rotate about acommon axis, preferably independently, preferably under low torque. Inone form, the swivel may be constructed to rotate through an angle of atleast 360 degrees. In another form, the swivel may be constructed torotate through an angle less than 360 degrees. When used in the contextof an air delivery conduit, the sub-assembly of components preferablycomprises a matched pair of cylindrical conduits. Preferably there islittle or no leak flow of air from the swivel in use.

Vent: (noun) the structure that allows a deliberate controlled rate leakof air from an interior of the mask, or conduit to ambient air, to allowwashout of exhaled carbon dioxide (CO₂) and supply of oxygen (O₂).

6.9 Other Remarks

Unless the context clearly dictates otherwise and where a range ofvalues is provided, it is understood that each intervening value, to thetenth of the unit of the lower limit, between the upper and lower limitof that range, and any other stated or intervening value in that statedrange is encompassed within the technology. The upper and lower limitsof these intervening ranges, which may be independently included in theintervening ranges, are also encompassed within the technology, subjectto any specifically excluded limit in the stated range. Where the statedrange includes one or both of the limits, ranges excluding either orboth of those included limits are also included in the technology.

Furthermore, where a value or values are stated herein as beingimplemented as part of the technology, it is understood that such valuesmay be approximated, unless otherwise stated, and such values may beutilized to any suitable significant digit to the extent that apractical technical implementation may permit or require it.

Unless defined otherwise, all technical and scientific terms used hereinhave the same meaning as commonly understood by one of ordinary skill inthe art to which this technology belongs. Although any methods andmaterials similar or equivalent to those described herein can also beused in the practice or testing of the present technology, a limitednumber of the exemplary methods and materials are described herein.

When a particular material is identified as being preferably used toconstruct a component, obvious alternative materials with similarproperties may be used as a substitute. Furthermore, unless specified tothe contrary, any and all components herein described are understood tobe capable of being manufactured and, as such, may be manufacturedtogether or separately.

It must be noted that as used herein and in the appended claims, thesingular forms “a”, “an”, and “the” include their plural equivalents,unless the context clearly dictates otherwise.

All publications mentioned herein are incorporated by reference todisclose and describe the methods and/or materials which are the subjectof those publications. The publications discussed herein are providedsolely for their disclosure prior to the filing date of the presentapplication. Nothing herein is to be construed as an admission that thepresent technology is not entitled to antedate such publication byvirtue of prior invention. Further, the dates of publication providedmay be different from the actual publication dates, which may need to beindependently confirmed.

Moreover, in interpreting the disclosure, all terms should beinterpreted in the broadest reasonable manner consistent with thecontext. In particular, the terms “comprises” and “comprising” should beinterpreted as referring to elements, components, or steps in anon-exclusive manner, indicating that the referenced elements,components, or steps may be present, or utilized, or combined with otherelements, components, or steps that are not expressly referenced.

The subject headings used in the detailed description are included onlyfor the ease of reference of the reader and should not be used to limitthe subject matter found throughout the disclosure or the claims. Thesubject headings should not be used in construing the scope of theclaims or the claim limitations.

Although the technology herein has been described with reference toparticular embodiments, it is to be understood that these embodimentsare merely illustrative of the principles and applications of thetechnology. In some instances, the terminology and symbols may implyspecific details that are not required to practice the technology. Forexample, although the terms “first” and “second” may be used, unlessotherwise specified, they are not intended to indicate any order but maybe utilised to distinguish between distinct elements. Furthermore,although process steps in the methodologies may be described orillustrated in an order, such an ordering is not required. Those skilledin the art will recognize that such ordering may be modified and/oraspects thereof may be conducted concurrently or even synchronously.

It is therefore to be understood that numerous modifications may be madeto the illustrative embodiments and that other arrangements may bedevised without departing from the spirit and scope of the technology.

7 ASPECTS

In the following, additional and/or alternative aspects of the inventionare listed.

1. An apparatus for treating a respiratory disorder comprising:

a housing;

a user interface display;

a pressure source to provide a supply of pressurized gas;

a controller configured to control the pressure source;

a power source connection configured to receive an electrical connectionof a power source to provide a supply of power for the apparatus; and

a plurality of external batteries electrically connected in a series tothe power source connection.

2. The apparatus according to aspect 1, wherein the controller isconfigured to detect the connection of the plurality of externalbatteries and control the supply of power to the apparatus.

3. The apparatus according to any one of aspects 1 to 2, wherein in usethe external battery of the plurality of external batteries being usedto provide the supply of power for the apparatus is the power supplyingexternal battery and each of the plurality of external batteries areused as the power source sequentially with the external battery closestto the power source connection being the last external battery to beused as the power source.4. The apparatus according to any one of aspects 1 to 3, wherein eachexternal battery of the plurality of external batteries is connected toan adjacent external battery using an electrical cable.5. The apparatus according to any one of aspects 1 to 4, furthercomprising an internal battery configured to be received within thehousing and in use the internal battery is used as the power sourceafter all the power from the external batteries is depleted.6. The apparatus according to any one of aspects 1 to 5, wherein analternating current (AC) power supply is connectable in the series tothe plurality of external batteries, and in use when the AC power supplyis connected the AC power supply is used as the power source.7. The apparatus according to any one of aspects 1 to 5, wherein adirect current (DC) power supply is connectable in the series to theplurality of external batteries, and in use when the DC power supply isconnected the DC power supply is used as the power source.8. The apparatus according to any one of aspects 1 to 7, wherein uponreceiving a power capacity request from the controller each of theplurality of external batteries is capable of determining an estimate ofits own remaining capacity.9. The apparatus according to aspect 8, wherein the external batteriesremaining capacity is used to determine an estimate of a total externalbatteries remaining run time.10. The apparatus according to aspect 9, wherein the total externalbatteries remaining run time is determined as a function of theremaining capacity of each external battery and the remaining run timeof the power supplying external battery.11. The apparatus according to any one of aspects 8 to 10, wherein theplurality of external batteries includes an upstream external batteryand a downstream external battery, wherein the downstream externalbattery is electrically connected to the power source connection and theupstream external battery is electrically connected in the series to thedownstream external battery.12. The apparatus according to aspect 11, wherein the downstreamexternal battery is connected to the power source connection using anelectrical cable.13. The apparatus according to any one of aspects 10 or aspect 11,wherein one or more further external batteries are electricallyconnected between the downstream external battery and the upstreamexternal battery.14. The apparatus according to any one of aspects 11 to 13, wherein theupstream external battery is configured to send the determined estimateof the upstream external batteries remaining capacity to the downstreamexternal battery.15. The apparatus according to aspect 14, wherein each of the one ormore further external batteries are configured to send the determinedestimate of the external battery remaining capacity along the series tothe downstream external battery.16. The apparatus according to any one of aspects 14 to 15, wherein thedownstream external battery is configured to determine a total externalbattery remaining capacity from all of the external batterieselectrically connected in the series.17. The apparatus according to any one of aspects 14 to 16, wherein thedownstream external battery is configured to determine a total externalbattery remaining run time from all of the external batterieselectrically connected in the series as a function of a remaining runtime of the power supplying external battery.18. The apparatus according to any one of aspects 5 and 6 to 17 whendependent upon aspect 5, wherein upon receiving a remaining capacityrequest from the controller the internal battery is capable ofdetermining an estimate of the internal battery remaining capacity.19. The apparatus according to aspect 18, wherein the internal batteryremaining capacity is used to determine an estimate of internal batteryremaining run time.20. The apparatus according to aspect 19, wherein the internal batteryremaining run time is determined as a function of a remaining run timeof the internal battery when the internal battery is being used toprovide the power to run the apparatus or the power supplying externalbattery when one of the plurality of external batteries is being used torun the apparatus.21. The apparatus according to any one of aspects 18 to 20 whendependent upon any one of aspects 8 to 17, wherein the controller isconfigured to calculate an estimate of a total battery remainingcapacity of the plurality of external batteries and the internalbattery.22. The apparatus according to any one of aspects 18 to 21 whendependent upon any one of aspects 8 to 17, wherein the controller isconfigured to calculate an estimate of a total battery remaining runtime of the plurality of external batteries and the internal battery.23. The apparatus according to any one of aspects 21 to 22, wherein theuser interface display is configured to display the estimate of thetotal battery remaining capacity and/or the estimate of the totalbattery remaining run time.24. The apparatus according to anyone of aspects 1 to 23, wherein theapparatus is a ventilator.25. A method of determining an estimate of a total available batterycapacity from two or more battery power sources electrically connectedto a respiratory device, the respiratory device comprising a controllerconfigured to perform the method of:

request an estimate of available capacity from a first battery powersource to provide a first battery capacity;

request an estimate of available capacity from a second battery powersource to provide a second battery capacity; and

combine the first battery capacity and the second battery capacity todetermine an estimate of the total available battery capacity.

26. The method according to aspect 25, wherein the total availablebattery capacity is an estimate of a total state of charge from thefirst battery source and the second battery source.

27. The method according to any one of aspects 25 to 26, wherein thefirst battery source is at least one external battery electricallyconnected to the respiratory device and the second battery source is aninternal battery located within the respiratory device.28. The method according to aspect 27, wherein the first battery sourceincludes a plurality of external batteries connected in series, each ofthe plurality of external batteries including an input port and outputport configured to receive an electrical cable therebetween.29. The method according to aspect 28, wherein the plurality of externalbatteries includes a downstream external battery, the output port of thedownstream external battery is electrically coupled to the respiratorydevice via an electrical cable and the input port of the downstreamexternal battery is electrically coupled via an electrical cable to theoutput port of a second external battery of the plurality of externalbatteries.30. The method according to aspect 29, wherein each of the plurality ofexternal batteries are electrically coupled to an adjacent externalbattery via an electrical cable connected between the input port of oneof the plurality of external batteries and the output port of theadjacent external battery.31. The method according to aspect 30 wherein each external batteryprovides an estimate of available capacity and sends the availablecapacity via the electrical cables along the series to the downstreamexternal battery.32. The method according to any one of aspects 25 to 31, wherein whenthe first battery source is the battery being used to provide power tothe respiratory device, a total remaining run time is calculated as afunction of the remaining run time of the first battery and the totalavailable battery capacity.33. The method according to any one of aspects 25 to 32, furthercomprising displaying the total available battery capacity on a userinterface display of the respiratory device.34. A respiratory device to provide a supply of breathable gas to apatient breathing in successive cycles, each cycle including aninspiration phase and an expiration phase, the respiratory devicecomprising:

a blower including a motor configured to accelerate to reach aninspiration pressure provided during the inspiration phase anddecelerate to reach an expiration pressure provided during theexpiration phase;

a first power source arranged to provide a supply of power to run themotor of the blower; and

an energy storage unit configured to store energy generated by the motorwhen the motor decelerates;

wherein when a voltage present in the energy storage unit exceeds afirst threshold, the supply of power from the first power source to themotor is turned off and the motor is energized by the energy in theenergy storage unit and when the voltage in the energy storage unitfalls below a second threshold the supply of power from the first powersource to the motor is turned on.

35. The respiratory device according to aspect 34, wherein the energystorage unit includes at least one capacitor or super capacitor.

36. The respiratory device according to aspects 34 to 35, furthercomprising a regulator switch that monitors the voltage of the energystorage unit and switches the supply of power to the motor from thefirst power source on and off.

The invention claimed is:
 1. A respiratory device to provide a supply ofbreathable gas to a patient breathing in successive cycles, each cycleincluding an inspiration phase and an expiration phase, the respiratorydevice comprising: a blower including a motor configured to accelerateto reach an inspiration pressure provided during the inspiration phaseand decelerate to reach an expiration pressure provided during theexpiration phase; a first power source arranged to provide a supply ofpower to run the motor of the blower; and an energy storage unitconfigured to store energy generated by the motor when the motordecelerates; wherein when a voltage present in the energy storage unitexceeds a first threshold, the supply of power from the first powersource to the motor is turned off and the motor is energized by theenergy in the energy storage unit and when the voltage in the energystorage unit falls below a second threshold the supply of power from thefirst power source to the motor is turned on.
 2. The respiratory deviceaccording to claim 1, wherein the energy storage unit includes at leastone capacitor or super capacitor.
 3. The respiratory device according toclaim 1, further comprising a regulator switch that monitors the voltageof the energy storage unit and switches the supply of power to the motorfrom the first power source on and off.
 4. The respiratory deviceaccording to claim 2, further comprising a regulator switch thatmonitors the voltage of the energy storage unit and switches the supplyof power to the motor from the first power source on and off.
 5. Therespiratory device according to claim 3, wherein the regulator switch isa voltage boost regulator.
 6. The respiratory device according to claim1, wherein the energy storage unit includes at least one capacitor, agroup of capacitors or super capacitors, or a battery.
 7. Therespiratory device according to claim 1, further comprising a controlsystem.
 8. The respiratory device according to claim 1, wherein theenergy storage unit is positioned in parallel with the first powersource.
 9. The respiratory device according to claim 1, wherein a diodeis located between the energy storage unit and the first power source.10. The respiratory device according to claim 1, wherein the first powersource includes an external input supply and/or an internal battery. 11.The respiratory device according to claim 10, wherein the external inputsupply includes any one of an AC mains power supply, DC Main powersupply, or an external battery.
 12. The respiratory device according toclaim 1, further comprising a motor driver.
 13. A method of operating arespiratory device to provide a supply of breathable gas to a patientbreathing in successive cycles, each cycle including an inspirationphase and an expiration phase, the method comprising: providing a blowerincluding a motor configured to accelerate to reach an inspirationpressure provided during the inspiration phase and decelerate to reachan expiration pressure provided during the expiration phase; providing afirst power source arranged to provide a supply of power to run themotor of the blower; storing energy generated by the motor in an energystorage unit when the motor decelerates; turning off the supply of powerfrom the first power source to the motor when a voltage present in theenergy storage unit exceeds a first threshold and energizing the motorby the energy stored in the energy storage unit; and turning on thesupply of power from the first power source to the motor when thevoltage in the energy storage unit falls below a second threshold. 14.The method according to claim 13, wherein energy generated by the motoris stored in the energy storage unit when the motor cycles from aninspiration pressure to an expiration pressure.
 15. The method accordingto claim 13, wherein a diode is located between the energy storage unitand the first power source, and the diode is used to provide power tothe blower.
 16. The method according to claim 13, further comprising acontrol system that is powered from the first power source.